Determining initial treatments from spectral data

ABSTRACT

This document presents a system for managing treatment for an emergency cardiac event. The system includes memory, one or more electronic ports for receiving ECG signals, and a treatment module executable on one or more processing devices. The module is configured to generate transform values for a time segment of ECG, obtain one or more previous values derived from one or more earlier time segments of the ECG, and determine, based on the generated transform values, and the one or more previous values, at least one of: a) a future therapeutic action for treating the emergency cardiac event, or b) a phase of the cardiac event. The module is further configured to cause one or more output devices to present an indication of at least one of the therapeutic action or the phase of the cardiac event.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation application of and claims priority to U.S. application Ser. No. 14/736,079, filed on Jun. 10, 2015, which claims priority to U.S. Provisional Application 62/010,215, filed on Jun. 10, 2014, and U.S. Provisional Application 62/011,902, filed on Jun. 13, 2014. This application is also related to the co-filed utility application which claims priority to U.S. Provisional Application 62/010,202, filed on Jun. 10, 2014. The content of each of the above referenced applications is incorporated herein by reference.

TECHNICAL FIELD

This document relates to cardiac resuscitation systems and techniques.

BACKGROUND

Heart attacks are a common cause of death. A heart attack occurs when a portion of the heart tissue loses circulation and, as a result, becomes damaged (e.g., because of blockage in the heart vasculature). Heart attacks and other abnormalities can lead to ventricular fibrillation (VF), which is an abnormal heart rhythm (arrhythmia) that causes the heart to lose pumping capacity. If such a problem is not corrected quickly—typically within minutes—the rest of the body loses oxygen and the person dies. Therefore, prompt care of a person undergoing ventricular fibrillation can be key to a positive outcome for such a person.

One common way to treat ventricular fibrillation is through the use of an electrical defibrillator that delivers a relatively high voltage shock to the heart in order to force it back to a normal, consistent, and strong rhythm. People who have had previous problems with ventricular fibrillation may be implanted with an automatic defibrillator that constantly monitors the condition of their heart and applies a shock when necessary. Other such people may be provided with a wearable defibrillator in the form of a vest such as the LIFEVEST product from ZOLL Medical Corporation. Other people may be treated using an external defibrillator, such as in a hospital or via an automatic external defibrillator (AED) of the kind that is frequently seen in airports, public gymnasiums, and other public spaces. Defibrillation may be delivered in coordination with cardiopulmonary resuscitation, which centers around the provision of repeated compressions to a victim's chest, such as be a rescuer pressing downward repeatedly with the palms of the hands, or via a mechanical compression device such as the AUTOPULSE non-invasive cardiac support pump from ZOLL Medical Corporation.

People undergoing ventricular fibrillation may be more receptive to a defibrillating shock in some instances compared to others. For example, research has determined that an indication of whether a shock that is delivered will likely result in successful defibrillation can be obtained using a computation of amplitude spectrum area (AMSA), or other computational methods that use either time-based or spectrum-based analytic methods to calculate, from an electrocardiogram (ECG), a prediction of defibrillation shock success.

SUMMARY

This document describes systems and techniques that may be used to help determine when a shock on a person suffering from VF will likely be successful, i.e., will defibrillate the person. Such systems and techniques may also be used to determine where, time-wise, a person is in the process of suffering from cardiac arrest and fibrillation, since defibrillating shocks may be much less effective after a person has been fibrillating for several minutes, and CPR (including forceful CPR) may be a preferred mode of treatment instead. Techniques for making such predictions more accurately are also described herein.

Such determinations may then be used to guide someone (e.g., a physician, EMT, or lay rescuer) who is performing rescue operations on the person suffering VF (also referred to here as a patient or victim), such as by a portable defibrillator providing an indication, on a graphical display of the defibrillator or another device or audibly, that a shock should or should not be provided, or that chest compressions of a particular type should be given instead of a shock. Also, a device may display an estimated time since the fibrillations began so as to provide further information to a rescuer. In implementations described below, for example, such systems and techniques may take into account the success or lack of success in prior attempts to defibrillate the person (e.g., where there has been recurrent or refractory VF—where recurrent VF results after a successful prior defibrillating shock and refractory VF results after an unsuccessful prior defibrillating shock), among other factors, such as a current AMSA value for the person and trans-thoracic impedance level of the person.

Such systems may also take into account a current AMSA value (e.g., for recommending a shock) in combination of a trend in AMSA value over time (e.g., for recommending chest compressions instead of a shock). AMSA is a value calculated by taking a Fast Fourier Transform (FFT) of the VF waveform. While FFTs are generally premised on an assumption of an infinitely long time series, relatively short time series (e.g., less than 4 seconds and more preferably close to 1 second) may be better for predicted a likelihood of defibrillation. But short windows are generally inimical to proper operation of an FFT. As described below, a tapered window, such as a Tukey window, may be used to lessen edge effects from the windowing of ECG data that is collected for performing the AMSA calculation, which may permit the relative benefits of using a smaller window while lessening the dis-benefits of using the smaller window.

As one example of using AMSA values to make a determination of the likelihood that a currently-delivered shock with result in successful defibrillation, a threshold AMSA value may be set, at which level the shocking ability of a defibrillator is made available to a rescuer, or at which a likelihood of success that is displayed to the rescuer may change (e.g., AMSA values between X and Y may show a likelihood of m percent, while AMSA values between Y and Z may show a likelihood value of n percent) based on whether prior successful defibrillating shocks that have been given to a patient have been successful. For example, the relevant AMSA threshold for generating a certain output or action of a defibrillator (such as the display to the user just mentioned) may be adjusted based on determinations about the success of prior shocks and on the trans-thoracic impedance.

Thus, for example, an AMSA value or values may be computed from incoming ECG signals from the person, and decisions may be made by comparing the computed AMSA value to stored thresholds, where the thresholds may change based on the other factors, or the AMSA value may be adjusted using the other factors and then be compared to thresholds that do not change. Generally, there is no practical difference between changing the value and making static the thresholds against which it is compared versus changing the thresholds and leaving the value set.

Such adjustments, when based on determinations about the success or lack of success of prior defibrillation efforts, may be made in a variety of ways. For example, AMSA threshold values (which are reduced for recurrent VF) associated with future successful defibrillation have been determined to fall substantially when there has been a prior successful defibrillation during an emergency with a particular patient. (Unless indicated otherwise, all values that are collected, computed, and compared here are for a single adverse cardiac event for a patient.)

Such correlations may be determined by analysis of historical defibrillation activity (e.g., collected by portable defibrillators deployed in the field for actual cardiac events), and may be used to produce a mapping between observed past likelihood of success for various AMSA values and levels of prior successful defibrillations. Such data may be used, for example, to generate a look-up table or similar structure that can be loaded on other deployed (e.g., via network and/or wireless data updates) or to-be-deployed defibrillators, which can be consulted in the future during other cardiac events. For example, the number of prior successful defibrillations for an event may be along one axis of a table, and an AMSA score may be along another, and those other defibrillators may employ both values for a victim, with the table producing an indication of a likelihood of a to-be-applied shock being successful. The table or other data structure may also have additional dimensions, such as a dimension that identifies trans-thoracic impedance, and dimensions that identify other variables whose values that have been determined to be relevant to whether an applied shock will likely be successful.

As noted, a tapering function may be applied to the ECG data, so as to improve the accuracy of the FFT applied to the data, by preventing the data from jumping immediately from a zero value up the measured values, and then back down immediately to a zero value at the end of a measured window. Various parameters for the tapering function may also be applied, such as coefficients to define the slops of the starting and ending edges of the function. The particular type of tapering function used and the coefficients applied to it may be determined by analysis of ECG data and shock outcomes from prior rescue efforts that have been sensed and stored by on-site monitors (e.g., as part of portable defibrillators), and analyzed after-the-fact as a group to identify correlations between particular AMSA values, window sizes, window shapes, and defibrillation outcomes.

In certain other implementations, multiple different tapering functions may be applied to the same data essentially simultaneously, and the resulting AMSA value from one of the functions may be selected, or an AMSA value may be generated that is a composite from multiple different tapering functions. The window function that is used, the length of the window, and the coefficients for the window may also be adjusted dynamically, so that one or more of them change during a particular incident, or deployment, with a particular patient. For example, it may be determined from analysis of prior data that a certain window shape, size, and/or coefficients are better earlier in an episode of VF than later, so that a defibrillator may be programmed to change such parameters over the course of an event. Such changes may be tied to an initial determination about how long the patient has been in VF, which may be a function of user input (e.g., when the emergency call was made) and parameters measured by the defibrillator. Also, changes to the window type, size, and coefficients may be made from readings dynamically made from the patient under treatment. For example, AMSA values in a particular range may be measured better by a particular window type, size, or range of coefficients, so that an AMSA measurement made at time n that shows such a value, may be measured using the other parameters known to work best with that AMSA value at time n+1. Other techniques for dynamically adjusting the window type, window size, and/or coefficients may also be employed. The shape of the window may be asymmetric. For instance, the edge of the window that is “older” in time may have a window shape that results in a greater level of attenuation that the “newer” portion of the windowed data.

Upon a defibrillator making a determination of a likelihood of future success for defibrillating a patient, the defibrillator may provide an indication to a rescuer about such a determination. For example, the defibrillator may only allow a shock to be performed when the indication is sufficiently positive (e.g., over a set percentage of likelihood of success)—and may only provide a “ready for shock” light or other indication in such a situation. Also, a defibrillator may provide a display—such as a graphic that shows whether defibrillation will likely succeed (e.g., above a predetermined threshold level of likelihood of success) or provide a number (e.g., a percentage of likelihood of success) or other indication (e.g., a grade of A, B, C, D, or F) so that the rescuer can determine whether to apply a shock. In some situations, the AMSA value may serve merely to provide a recommendation to the user, with the user able to apply a shock at any time; in other situations (e.g., especially for AEDs to be used by lay rescuers), the AMSA value may be used to disable or enable the ability to deliver a shock.

The device (e.g., defibrillator) can also change the indication it presents in different situations, e.g., a dual-mode defibrillator could simply indicate whether defibrillation is advised (and may refuse to permit delivery of a shock when it is not advised) when the defibrillator is in AED mode, and may provide more nuanced information when the defibrillator is in manual mode, and thus is presumably being operated by someone who can better interpret such nuanced information and act properly on it.

With respect to indications of where a victim is in the process of a VF episode—e.g., how many minutes since the victim's episode has started—an average AMSA value may be determined over a time period so as to identify more generalized changes in the victim's AMSA values, rather than AMSA at a particular point in time or small slice of time. For example, AMSA values can be computed for particular points in time or particular windows in time and those values can be saved (e.g., in memory of a patient monitor or defibrillator). After multiple such measurements and computations have been made, an average may be computed across multiple such values. Because AMSA generally falls (on average) over time in an episode, if the average for a certain number of readings (e.g., a moving average) falls below a particular value or falls below the value over a minimum time period (so as to indicate the general AMSA condition of the victim rather than just a transient reading), the device may provide additional feedback to a rescuer.

These general phases of cardiac arrest or VF may be identified, in one representation, as three separate phases (though there may be some overlap at the edges of the phases): electrical, circulatory, and metabolic. The electrical phase is the first several minutes of an event, and marks a period during which electric shock can be particularly effective in defibrillating the victim's heart and returning the victim to a relative satisfactory condition. The circulatory phase appears to mark a decrease in effectiveness for electric shock in defibrillating the victim, and particularly in the absence of chest compressions performed on the victim. As a result, a device such as a portable defibrillator may be programmed to stop advising shocks during such a phase (or may advise a shock only when other determinations indicate that a shock would be particularly likely to be effective) and may instead advise forceful CPR chest compressions. Such forceful compressions may maximize blood flow through the heart tissue and other parts of the body so as to extend the time that the victim may survive without lasting or substantial damage.

In the metabolic phase, chest compressions may be relatively ineffective as compared to the circulatory phase. For example, where tissue has become ischemic, such as in circulatory phase, the tissue may react favorably to the circulation of blood containing some oxygen, but where tissue has become severely ischemic, such as in metabolic phase, the introduction of too much oxygen may be harmful to the tissue. As a result, more gentle compressions for the first period, such as 30 seconds, may need to be advised in the metabolic phase before the rescuer (or a mechanical chest compressor controlled to provide appropriate levels of compression following the points addressed here) uses a full force.

Other treatments that may be useful in the metabolic phase include extracorporeal circulation and cooling, either alone, in combination with each other, or in combination with other pharmacological treatments. In any event, observation of elapsed time since an event has begun and/or observation of the phase in which a victim is in, may be used to control a device or instruct a rescuer to switch from a first mode of providing care to a second mode of providing care in which the parameters of the provided care differ (e.g., speed or depth of chest compressions may change, temperature-based therapy may be provided or stopped, or pharmaceuticals may be administered).

In certain implementations, such systems and techniques may provide one or more advantages. For example, determinations of whether a shock should be provided or what advice to provide a rescuer based on the phase a victim is in can be made from values that are already being measured for a patient (e.g., trans-thoracic impedance may already be used by a defibrillator to affect the shape of the voltage of the waveform that is provided to the patient). For example, determinations about shocks may be improved compared to simply measuring AMSA, and may thus result in better performance for a system and better outcomes for a patient. In particular, a defibrillator may cause a rescuer to wait to provide a defibrillating shock until a time at which the shock is more likely to be effective. As a result, the patient may avoid receiving an ineffective shock, and then having to wait another cycle for another shock (which may end up being equally ineffective). And a system may guide the rescuer in providing a shock, versus providing deep chest compressions, versus providing progressive chest compressions (or may cause a device to provide such actions automatically), throughout the course of a cardiac event. Such a process may, therefore, result in the patient returning to normal cardiac function more quickly and with less stress on his or her cardiac system, which will generally lead to better patient outcomes.

The use of particular type, duration, and coefficients for making AMSA readings may result in more accurate instructions being given to a human or mechanical rescuer, or in enabling or disabling functionality of a medical device. In particular, the feedback provided may result in determinations about whether to shock or not shock, or to provide chest compressions, may be more closely aligned with a likelihood of a positive outcome (e.g., defibrillation) for a particular patient, and may be customized to the present situation of the patient (e.g., as indicated by AMSA readings for the patient).

In one implementation, a system for managing treatment for an emergency cardiac event, includes memory and one or more electronic ports for receiving signals from sensors for obtaining indications of an electrocardiogram (ECG) for a patient. The system also includes a patient treatment module executable on one or more processing devices, wherein the patient treatment module is configured to generate transform values for a time segment of ECG. The transform values represent magnitudes of two or more frequency components of the ECG. The patient treatment module is also configured to obtain one or more previous values derived from one or more earlier time segments of the ECG, determine, based on the generated transform values, and the one or more previous values, at least one of: a) a future therapeutic action for treating the emergency cardiac event, or b) a phase of the cardiac event. The patient treatment module is further configured to cause one or more output devices to present an indication of at least one of the therapeutic action or the phase of the cardiac event.

In another aspect, a system for treating a patient in cardiac arrest includes memory, and one or more electronic ports for receiving signals from sensors for obtaining indications of an electrocardiogram (ECG) for the patient. The system also includes a patient treatment module executable on one or more processing devices. The patient treatment module is configured to generate transform values that represent magnitudes of two or more frequency components of the ECG, generate a time series from a plurality of the transform values, and determine, based on the time series, a future therapeutic action for treating the cardiac arrest.

In another aspect, a system for managing treatment for an emergency cardiac event includes memory, and one or more electronic ports for receiving signals from sensors for obtaining indications of an electrocardiogram (ECG) for a patient. The system also includes a patient treatment module executable on one or more processing devices. The patient treatment module is configured to generate transform values for a time segment of ECG, wherein the transform values represent magnitudes of two or more frequency components of the ECG. The patient treatment module is also configured to obtain one or more previous transform values derived from one or more earlier time segments of the ECG, determine, based on the generated transform values, and the one or more previous transform values, an indication of a likelihood of success from delivering a defibrillating shock, and cause one or more output devices to present the indication of a likelihood of success from delivering a defibrillating shock.

In another aspect, this document features one or more machine-readable storage devices having encoded thereon machine readable instructions for causing one or more processors to perform various operations. The operations include receiving, signals indicative of an electrocardiogram (ECG) of a patient, and generating transform values for a time segment of the ECG, wherein the transform values represent magnitudes of two or more frequency components of the ECG. The operations also include obtaining one or more previous values derived from one or more earlier time segments of the ECG, determining, based on the generated transform values, and the one or more previous values, a future therapeutic action for treating an emergency cardiac event in the patient, and causing one or more output devices to present an indication of at least one of the therapeutic action or the phase of the cardiac event.

In another aspect, this document features one or more machine-readable storage devices having encoded thereon machine readable instructions for causing one or more processors to perform various operations that include receiving signals indicative of an electrocardiogram (ECG) of a patient, and generating transform values. The transform values represent magnitudes of two or more frequency components of the ECG. The operations also include generating a time series from a plurality of the transform values, and determining, based on the time series, a future therapeutic action for treating a cardiac arrest of the patient.

In another aspect, this document features one or more machine-readable storage devices having encoded thereon machine readable instructions for causing one or more processors to perform various operations that include receiving, signals indicative of an electrocardiogram (ECG) of a patient, and generating transform values. The transform values represent magnitudes of two or more frequency components of the ECG. The operations also include obtaining one or more previous transform values derived from one or more earlier time segments of the ECG, determining based on the generated transform values, and the one or more previous transform values, an indication of a likelihood of success from delivering a defibrillating shock, and causing one or more output devices to present the indication of a likelihood of success from delivering a defibrillating shock.

Implementations of the above aspect can include one or more of the following features.

The patient treatment module can include an ECG analyzer for generating an amplitude spectrum area (AMSA) value using the transform values. The previous values can be derived from one or more earlier time segments of the ECG are AMSA values. The transform values can be updated at a rate of 0.1-10 Hz. The length of the time segment can be in the range between about 1 and 4 seconds. The one or more processing devices can generate the transform values for the time segment of ECG using a tapered window. The tapered window can be one of: a Tukey window, a Hann window, a Blackman-Harris window, or a Flat Top window. The future therapeutic action can be determined based at least in part on comparing a value obtained from the generated transform values to a threshold. The transform can include at least one of: Fourier, fast Fourier, discrete Fourier, Hilbert, discrete Hilbert, wavelet, and discrete wavelet methods. The therapeutic action can include computing an average based on the one or more previous values. The average can be also based on a value obtained from the generated transform values. The one or more previous values can be generated via processing of multiple earlier time segments of the ECG. The processing can be performed two or more times during the cardiac event. The one or more output devices can present an audible or visual feedback of at least one of the indication of the therapeutic action or the phase of the cardiac event. The therapeutic action can include delivering a defibrillating shock to the patient. The therapeutic action can include initiating or continuing cardiopulmonary resuscitation (CPR). The therapeutic action can include adjusting a cardiopulmonary resuscitation (CPR) technique. The phase can be one of: an electrical phase, a circulatory phase, or a metabolic phase. The one or more output devices can present a visual or audible feedback based on the generated transform values and the previous values. The feedback includes an indication of a likelihood of success from delivering a defibrillating shock. The future therapeutic action or the phase of the cardiac event can be generated based on one or more additional parameters. The one or more additional parameters can include at least one of: trans-thoracic impedance (TTI), levels of prior successful defibrillations, and a trend in AMSA values over time.

The transform values can include amplitude spectrum area (AMSA) values. The therapeutic action can be determined based on determining a trending of the transform values in the time series. The transform values can include normalized transform values. The transform can include a Fast Fourier Transform. The transform can include one or more of: Fourier, discrete Fourier, Hilbert, discrete Hilbert, wavelet, and discrete wavelet methods. The transform can be a transform that uses zero crossing analysis.

In one implementation, a system for managing care of a person receiving emergency cardiac assistance is disclosed. The system comprises one or more capacitors for delivering a defibrillating shock to a patient; one or more electronic ports for receiving signals from sensors for obtaining indications of an electrocardiogram (ECG) for the patient; and a patient treatment module executable on one or more computer processors to provide a determination of a likelihood of success from delivering a future defibrillating shock to the person with the one or more capacitors, using (a) information about a prior defibrillating shock, and (b) a value that is a function of current ECG signals from the patient. The system can also include an output mechanism arranged to indicate, to a user of the system, an indication regarding the likelihood of success from delivering a defibrillating shock to the person with the one or more capacitors. The output mechanism can include a visual display, and the system can be programmed to display to the user one of multiple possible indications that each indicate a degree of likelihood of success. Alternatively or in addition, the output mechanism can comprise an interlock that prevents a user from delivering a shock unless the determined likelihood of success exceeds a determined value.

In some aspects, the patient treatment module comprises an ECG analyzer for generating an amplitude spectrum area (AMSA) value, wherein the patient treatment module uses the information about the level of success from the prior defibrillating shock to adjust the AMSA value. Moreover, the patient treatment module can comprise an ECG analyzer for generating indications of heart rate for the patent, heart rate variability for the patent, ECG amplitude for the patent, and/or first or second derivatives of ECG amplitude for the patent. The indication of ECG amplitude can comprise, for example, an RMS measurement, measure peak-to-peak, peak-to-trough, or an average of peak-to-peak or peak-to-trough over a specified interval.

In other aspects, the patient treatment module is programmed to determine whether a prior defibrillation shock was at least partially successful, and based at least in part on the determination of whether the prior defibrillation was at least partially successful, modify a calculation of the likelihood of success from delivering the future defibrillating shock. Moreover, determining a likelihood of success from delivering a future defibrillating shock to the person can depend on a determination of whether one or more prior shocks delivered to the person were successful in defibrillating the person. In addition, determining a likelihood of success from delivering a future defibrillating shock can comprise performing a mathematical transform on the ECG data. The mathematical transform can be selected from a group consisting of Fourier, discrete Fourier, Hilbert, discrete Hilbert, wavelet, and discrete wavelet methods. In some implementations, the determination of the likelihood of success can include a zero-crossing based analysis, an example of which is described in Kedem, Spectral Analysis and Discrimination by Zero-Crossings, Proceedings of the IEEE, Vol. 74, No 11, November 1986. Zero-crossing counts in filtered time series may be referred to as higher order crossings. In addition, determining a likelihood of success from delivering a future defibrillating shock comprises performing a calculation by an operation selected from a group consisting of logistic regression, table look-up, neural network, and fuzzy logic.

In yet another example, the patient treatment module is programmed to determine the likelihood of success from delivering a future defibrillating shock using at least one patient-dependent physical parameter separate from a patient ECG reading. The patient treatment module can also be programmed to determine the likelihood of success from delivering a future defibrillating shock using at a measure of trans-thoracic impedance of the person.

In another implementations, a method for managing care of a person receiving emergency cardiac assistance is disclosed, and comprises monitoring, with an external defibrillator, electrocardiogram (ECG) data from a person receiving emergency cardiac assistance; determining whether a prior defibrillation shock occurred; determining a likelihood of future defibrillation shock success using at least the ECG data; based at least in part on the determination of whether the prior defibrillation occurred, modifying the calculation of the chance of defibrillation shock success; and affecting control of the external defibrillator based on the identification of whether a present defibrillation shock will likely be effective. Determining a likelihood of future defibrillation shock success can comprise determining a value that is a function of electrocardiogram amplitude at particular different frequencies or frequency ranges. Determining a likelihood of future defibrillation shock success can comprise determining an amplitude spectrum area (AMSA) value for the ECG data, and can also comprise adjusting the determined AMSA value using information about the prior defibrillation shock. In addition, the method can comprise determining whether the adjusted AMSA value exceeds a predetermined threshold value.

In certain aspects, the method comprises providing to the rescuer a visual, audible, or tactile alert that a shockable situation exists for the person, if the adjusted AMSA value is determined to exceed the predetermined threshold value. The method can also include determining whether a prior defibrillation shock was at least partially successful, and based at least in part on the determination of whether the prior defibrillation was at least partially successful, modifying a calculation of the likelihood of success from delivering the future defibrillating shock. The determining of a likelihood of success from delivering a future defibrillating shock can comprise performing a mathematical transform on the ECG data, and the mathematical transform may be selected from a group consisting of Fourier, discrete Fourier, Hilbert, wavelet, and discrete wavelet methods. Also, determining a likelihood of success from delivering a future defibrillating shock can comprise performing a calculation by an operation selected from a group consisting of logistic regression, table look-up, neural network, and fuzzy logic. Moreover, the likelihood of success from delivering a future defibrillating shock can be determined using at least one patient-dependent physical parameter separate from a patient ECG reading.

In certain other aspects, the additional physiologic parameter is trans-thoracic impedance of the person receiving emergency cardiac care, and the indication of trans-thoracic impedance can be determined from signals sensed by a plurality of electrocardiogram leads that also provide the EGC data. The method may also include cyclically repeating the actions of monitoring, determining, identifying and providing the indication. The method also can comprise identifying compression depth of chest compressions performed on the person, using a device on the person's sternum and in communication with the external defibrillator, and providing feedback to a rescuer performing the chest compressions regarding rate of compression, depth of compression, or both.

In yet another implementation, there is disclosed a system for managing care of a person receiving emergency cardiac assistance that comprises one or more capacitors for delivering a defibrillating shock to a patient; one or more electronic ports for receiving signals from sensors for obtaining indications of an electrocardiogram (ECG) for the patient; and a patient treatment module executable on one or more computer processors to identify an phase in which a patient being monitored by the system is in relative to a time at which an adverse cardiac event for patient began. The phase in which the patient being monitored by the system is in can includes an elapsed time since the adverse cardiac event for the patient began, and a phase selected from an electrical, circulatory, and metabolic phase. The system may also comprise an output mechanism arranged to indicate, to a user of the system, an indication regarding the phase in which the patient is in. The output mechanism can comprise a visual display, and the system can be programmed to display to the user one indication of multiple possible indications, wherein the one indication indicates to the user the phase in which the patient is in.

In certain aspects, the system is programmed to display instructions for the user to care for the patient, the instructions selected to correspond to the phase in which the patient is in. Also, the output mechanism can include an interlock that prevents a user from delivering a shock unless a determined likelihood of success of a shock reviving the patient exceeds a determined value. In other aspects, the patient treatment module comprises an ECG analyzer for generating an amplitude spectrum area (AMSA) value, an indication of heart rate for the patent, an indication of heart rate variability for the patent, or an indication of ECG amplitude for the patent.

In yet other aspects, the indication of ECG amplitude comprises an RMS measurement, measured peak-to-peak, peak-to-trough, or an average of peak-to-peak or peak-to-trough over a specified interval. Also, the patient treatment module can include an ECG analyzer for generating an indication of a first derivative of ECG amplitude for the patent, or an indication of a second derivative of ECG amplitude for the patent. Moreover, the patient treatment module can be programmed to determine whether a defibrillation shock, prior to a future defibrillation shock being consider for delivery, was at least partially successful, and based at least in part on the determination of whether the prior defibrillation shock was at least partially successful, modifying a calculation of a likelihood of success for delivering the future defibrillation shock.

In another implementation, a method for managing care of a person receiving emergency cardiac assistance is disclosed and comprises monitoring, with an external defibrillator, electrocardiogram (ECG) data from a person receiving emergency cardiac assistance; performing a mathematical transform of the ECG data from a time domain to a frequency domain using a tapered window in the time domain; determining a likelihood of future defibrillation shock success using at least the mathematical transformation; and affecting control of the external defibrillator based on the identification of whether a present defibrillation shock will likely be effective. The tapered window can comprise a Tukey window, and can be between about one second and about 2 seconds wide. The tapered window can be selected from a group consisting of Tukey, Hann, Blackman-Harris, and Flat Top, and the mathematical transform can comprise a Fast Fourier Transform.

In certain aspects, determining a likelihood of future defibrillation shock success comprises determining a value that is a function of electrocardiogram amplitude at particular different frequencies or frequency ranges. It may also comprise determining an amplitude spectrum area (AMSA) value for the ECG data. Also, determining a likelihood of future defibrillation shock success can further comprise adjusting the determined AMSA value using information about a prior defibrillation shock. Moreover, the method can additionally include determining whether the adjusted AMSA value exceeds a predetermined threshold value. In some aspects, the method also includes providing to a rescuer a visual, audible, or tactile alert that a shockable situation exists for the person receiving emergency cardiac assistance, if the adjusted AMSA value is determined to exceed the predetermined threshold value.

In yet other aspects, the method comprises determining whether a prior defibrillation shock was at least partially successful, and based at least in part on the determination of whether the prior defibrillation was at least partially successful, modifying a calculation of the likelihood of success from delivering the future defibrillating shock. In certain aspects, determining a likelihood of success from delivering a future defibrillating shock comprises performing a calculation by an operation selected from a group consisting of logistic regression, table look-up, neural network, and fuzzy logic. The likelihood of success can also be determined using at least one patient-dependent physical parameter separate from a patient ECG reading, and the additional patient-dependent parameter can comprise an indication of trans-thoracic impedance of the person receiving emergency cardiac care.

In additional aspects, the indication of trans-thoracic impedance is determined from signals sensed by a plurality of electrocardiogram leads that also provide the EGC data. The method can also comprise cyclically repeating the actions of monitoring, determining, identifying and affecting the control, and may also or alternatively include identifying compression depth of chest compressions performed on the person receiving emergency cardiac assistance, using a device on the person's sternum and in communication with the external defibrillator, and providing feedback to a rescuer performing the chest compressions, the feedback regarding rate of compression, depth of compression, or both. Also, the affecting control can include preventing a user from delivering a shock unless the determination of whether a shock will be effective exceeds a determined likelihood level, and/or electronically displaying, to a user, an indicator of the determined indication of whether a shock will be effective. In addition, displaying an indicator can include displaying a value, of multiple possible values in a range that indicates a likelihood of success. Moreover, the calculation of the likelihood of current shock success can be determined or modified using a determination of a value of trans-thoracic impedance of the person.

Other features and advantages will be apparent from the description and drawings, and from the claims.

DESCRIPTION OF DRAWINGS

FIG. 1A shows schematically the combination of various types of data in making a determination about likely effectiveness of a defibrillating shock.

FIG. 1B shows a victim of a cardiac event being treated with a portable defibrillator.

FIG. 1C is a graph that represents changes in AMSA during an event correlated to phases in the event.

FIG. 1D is a table showing examples relating AMSA to predicted likelihood of failure in defibrillating a victim who has or has not been previously defibrillated.

FIG. 1E is a schematic diagram of a data structure for correlating AMSA and defibrillation success to predicted outcomes for shocking a victim.

FIG. 1F is a table showing predictions of successful defibrillation for different AMSA threshold values in the instances of 1^(st) defibrillation attempts.

FIG. 1G is a table showing AMSA prior defibrillation for refractory and recurrent VF.

FIG. 1H is a table showing prediction of successful defibrillation for increasing AMSA threshold values in the instances of refractory VF.

FIG. 1I shows examples of window functions and resulting FFTs from those functions.

FIG. 1J is a graph of area under curve for different windows.

FIG. 1K is a graph of post-shock rhythm for different AMSA ranges.

FIG. 1L is a chart of AMSA values and statistics.

FIG. 2 is a schematic block diagram that shows a defibrillator with an electrode package and compression puck.

FIG. 3A is a flow chart of a process for providing a user with feedback regarding a likelihood that a defibrillating shock will be successful.

FIG. 3B is a flow chart of a process for identifying a phase in a cardiac event so as to provide guidance to a rescuer.

FIGS. 4A and 4B are graphs showing relationships between patient outcome and AMSA threshold values for groups of patients having different trans-thoracic impedance values.

FIGS. 5A and 5B illustrate a defibrillator showing certain types of information that can be displayed to a rescuer.

FIGS. 6A-6C show screenshots of a defibrillator display that provides feedback concerning chest compressions performed on a victim.

FIGS. 7A and 7B show screenshots providing feedback regarding a perfusion index created from chest compressions.

FIGS. 8A and 8B show screenshots with gradiated scales indicating target chest compression depths.

FIG. 9 shows a general computer system that can provide interactivity with a user of a medical device, such as feedback to a user in the performance of CPR.

DETAILED DESCRIPTION

In general, defibrillation is a common treatment for various arrhythmias, such as VF. However, there can be undesired side effects (e.g., heart tissue damage, skin burns, etc.) that follow an electrical shock. Other undesired side effects of electric shock therapy include unnecessary interruptions of chest compressions in the time required to deliver the shock. Added to this, the effectiveness of defibrillation can fall generally over the elapsed time of an episode—where an episode may be measured from the time when a victim first starts feeling symptoms of cardiac arrest or loses consciousness and falls down. (Generally, the time from onset of a lethal VF episode and unconsciousness is relatively short, on the order of less than one-half minute.) It is therefore desirable to predict whether defibrillation will be successful in restoring a regular heartbeat following onset of an arrhythmic episode, and/or to determine how long it has been since a cardiac event started or what stage of the event the patient is in (e.g., a first, second, or third stage or phase).

Such predictions can each be referred to as an “indicator of success” or, equivalently, a “success indication” within the context of the present disclosure. The prediction may be used so that a defibrillating shock is not provided when the chance of successful defibrillation is low, and instead a system will wait until the chance of successful defibrillation increases to an acceptable level, and until such a time, a rescuer can be instructed to provide other care such as regular chest compressions, forceful chest compressions, or other care.

Such a determination about likelihood of successful shock can be used to alter care in an automatic and/or manual manner. In an automatic manner, a defibrillator may be made incapable of delivering a shock unless a success indication is above a determined level. In a manual manner, the success indication may be shown to a rescuer, and the rescuer may determine whether to apply a shock or not based on the indication, or the system may provide other information to the rescuer. For example, the indication of success may show a percentage likelihood that a shock will succeed, or may be a less specific indicator, such as an indication of which phase (e.g., of three phases discussed above and below) the victim is currently in, so that the rescuer can immediately understand, from experience and training related to those phases, that defibrillation attempts are likely to be successful or not.

Additional information provided to a rescuer may take the form of instructions, such as instructions to perform chest compressions or some other action, where the action is selected from among a plurality of possible treatments based on the current phase for the victim. A system may also integrate both—e.g., locking out the ability to provide a shock until a threshold level is reached, and then showing the relative likelihood of success above that value. The likelihood of success can be shown in various manners, such as by showing an actual percentage, or showing two or more of a low, medium, or high likelihood of success, e.g., on an electronic display of a defibrillator.

In certain implementations described herein, the present disclosure is directed to systems and methods for predicting whether defibrillation will be effective using amplitude spectrum area (AMSA) or any other appropriate Shock Prediction Algorithms (SPA) using analysis of ECG data, and adjusting such SPA predictions based on either the existence of prior defibrillation shocks as well as observations of a patient's reaction to those defibrillating shocks. In particular, it has been observed that victims of cardiac fibrillation will successfully defibrillate for lower AMSA threshold values if they have been previously successfully defibrillated during the same rescue session. Thus, rather than treating each shock as a discrete event in analyzing the probability of success, the techniques described here take into account prior shock deliveries, and an observed response of the patient to those deliveries, in determining an AMSA value or other value that will indicate that a shock currently applied to the patient will likely be successful (or not) in defibrillating the patient. Such a determination may also be combined with determinations about trans-thoracic impedance (trans-thoracic impedance) of the patient, as discussed more fully below.

To obtain better predictive value for the AMSA values, the time window from which the ECG data for an AMSA determination is taken may be made relative small (e.g., between 3 and 4 seconds, between 2 and 3 seconds, and between 1 and 2 seconds), which will place the data as close to the current status of the patient as possible. Smaller windows may suffer from edge effects more-so than larger windows, so the shape and coefficients for the windows may also be selected to maximize predictive power of the method. For example, a Tukey window having appropriate coefficients, such as about 0.2, may be employed.

FIG. 1A shows schematically the combination 100 of various types of data in making a determination about likely effectiveness of a defibrillating shock. In a particular implementation one of the types of data may be used alone, or multiple of the types may be combined so as to create a composite likelihood—e.g., by giving a score to each type and a weight, and combining them all to generate a weighted composite score for a likelihood. In this example, a shock indication 116 is the outcome of a decision process that may be performed by a defibrillator alone or in combination with one or more pieces of ancillary equipment (e.g., a computing device such as a smartphone carried by a healthcare provider). The shock indication 116 can be provided to part of the defibrillator, e.g., via an analog or digital signal that represents the indication, so that the part of the defibrillator may cause a shock feature to be executed or to cause it to be enabled so that it can be manually executed by an operator of the defibrillator. The shock indication may also or alternatively be provided to the rescuer so as to indicate that the rescuer can or should cause a defibrillating shock to be delivered. (In the context of this disclosure, a defibrillating shock is one of a level designed to cause defibrillation, but it does not need to be successful in causing the defibrillation.)

The relevant inputs may obtain at least some of their data from signals generated by a pair of electrodes 102 that may be adhered to a patient's torso—above one breast and below the other, for example, in a typical manner. The electrodes may include leads for obtaining ECG data and providing such data for analysis for a number of purposes. In addition, a CPR puck 104 may be placed on a patient's sternum and may deliver signals indicative of acceleration of the puck, and thus of up-down acceleration of the patient's sternum, which may be integrated so as to identify a depth of compression by the rescuer (and can also be used more simply to identify whether the patient is currently receiving chest compressions or not).

In certain implementations, the shape of the window may be asymmetric. For instance, the edge of the window that is “older” in time may have a window shape that results in a greater level of attenuation that does the “newer” portion of the windowed data. Other asymmetric shapes may also be used, as appropriate, to generate data that best represents an accurate prediction of shock success.

The electrodes 102 may be electrically connected to an ECG unit 106, which may be part of a portable defibrillator and may combine data from different leads (e.g., 8 leads) in a familiar manner to construct a signal that is representative of the patient's ECG pattern. Such an ECG signal is often used to generate a visual representation of the patient's ECG pattern on a screen of the defibrillator. The ECG-related data may also be analyzed in various ways to learn about the current condition of the patient, including in determining what sort of shock indication to provide to control the defibrillator or to display to a rescuer.

As one such example, ECG data may be provided to an AMSA analyzer 108, which may nearly continuously and repeatedly compute an AMSA number or similar indicator that represents ECG amplitude at particular different frequencies and/or frequency ranges in an aggregated form (e.g., a numeral that represents a value of the amplitude across the frequencies). Generally, the goal is to identify a waveform in which amplitude of the VF signals is large, and in particular, relatively large in the higher frequency ranges. Similarly, power spectrum area can be measured and its value can be used as an input that is alternative to, or in addition to, an AMSA value for purposes of making a shock indication. As described in more detail above and below, a current AMSA value (or a combination of multiple values over a short period) can be used to determine whether a shock is likely to be successful, and a plurality of combined AMSA values, such as a running average computed many times over time (and each covering a time period longer than the time period for the first AMSA value) using a moving window may indicate how much time has elapsed since a cardiac event began and thus indicate which phase, of multiple phases during a VF event, the victim is in, where each phase calls for a different most-effective treatment sub-protocol. Also, when rescuers first arrive on a scene, several seconds of ECG data may be used to provide them an initial indication of the time since the event started and/or the phase in which the victim currently is in—e.g., by displaying a number of elapsed minutes or the name of one of multiple phases (like the three phases discussed above) on a display screen of a medical device such as a monitor or defibrillator/monitor.

The AMSA analyzer 108 may be programmed to perform the analysis of the ECG, and perhaps other, inputs so as to maximize the predictive value of the AMSA value, whether by affecting inputs to the AMSA determination, and/or making an AMSA determination and then adjusting the AMSA value that is generated from that determination. As one example, the size of the window from which ECG data is taken in making the calculation may be set to maximize the predictive value, such as by being about 1 second to about 1.5 seconds long. As another example, the shape of the window may be tapered, such as by being in the form of a Tukey or Hann window, rather than having vertical edges like a boxcar window. Similarly, the coefficients for the window, such as Chi2 and p may be set to maximize the expected predictive value of the calculation. The AMSA analyzer may also be programmed to change such values dynamically over the course of a particular VF incident, either by moving the values progressively as time elapses so as to make the values match known expected values for maximizing the predictive effect of the calculation, or to respond to particular readings, e.g., to use particular window length, form, or coefficients when an AMSA value is in a certain defined range.

A trans-thoracic impedance module 110 may also obtain information from sensors provided with the electrodes 102, which indicates the impedance of the patient between the locations of the two electrodes. The impedance can also be a factor in determining a shock indication as described in more detail below.

A defibrillation history success module 112 tracks the application of defibrillating shocks to the patient and whether they were successful in defibrillating the patient, and/or the level to which they were successful. For example, the module 112 may monitor the ECG waveform in time windows of various sizes for a rhythm that matches a profile of a “normal” heart rhythm, and if the normal rhythm is determined to be established for a predetermined time period after the application of a defibrillating shock, the module 112 may register the existence of a successful shock. If a shock is applied and a normal rhythm is not established within a time window after the delivery of the shock, the module 112 can register a failed shock. In addition to registering a binary value of success/fail, the module may further analyze the ECG signal to determine the level of the success or failure and may, for example, assign a score to the chance of success of each shock, such as a normalized score between 0 (no chance of success) and 1 (absolute certainty).

A CPR chest compression module 114 may receive signals about the motion of the puck 104 to determine whether chest compressions are currently being applied to the patient, and to determine the depth of such compressions. Such information may be used, for example, in giving a rescuer feedback about the pace and depth of the chest compressions (e.g., the defibrillator could generate a voice that says “push harder”). The presence of current chest compression activity may also signal the other components that a shock is not currently advisable, or that ECG data should be analyzed in a particular manner so as to remove residual artifacts in the ECG signal from the activity of the chest compressions.

Information about pharmacological agents 115 provided to a patient may also be identified and taken into account in providing a shock indication to a rescuer. Such information may be obtained manually, such as by a rescuer entering, via a screen on a defibrillator or on a tablet computer that communicates with the defibrillator, identifiers for the type of agent administered to a patient, the time of administration, and the amount administered. The information may also be obtained automatically, such as from instruments used to administer the particular pharmacological agents. The device that provides a shock indication may also take that information into account in identifying the likelihood that a shock will be successful if provided to the patient (e.g., by shifting up or down an AMSA threshold for measuring shock success likelihood), and for other relevant purposes.

One or more of the particular factors discussed here may then be fed to a shock indication module 116, which may combine them each according to an appropriate formula so as to generate a binary or analog shock indication. For example, any of the following appropriate steps may be taken: a score may be generated for each of the factors, the scores may normalized (e.g., to a 0 to 1 or 0 to 100 scale), a weighting may be applied to each of the scores to represent a determined relevance of that factor to the predictability of a shock outcome, the scores may be totaled or otherwise combined, and an indication can be determined such as a go/no go indication, a percentage of likely success, and other such indications.

In this manner then, the system 100 may take into account one or a plurality of factors in determining whether a shock to be delivered to a patient is likely to be successful. The factors may take data measured from a plurality of different inputs (e.g., ECG, trans-thoracic impedance, delivered agents, etc.), and may be combined to create a likelihood indication, such as a numerical score that is to be measured against a predetermined scale (e.g., 0 to 100% likelihood or A to F grade). Such determination may then be used to control an automatically-operated system (e.g., that delivers chest compressions mechanically), to limit operation of a manually-operated system (e.g., by enabling a shock that is triggered by a user pressing a button), or by simply providing information to a system whose shock is determined solely by a rescuer (e.g., for manual defibrillators in which the operator is a well-trained professional).

FIG. 1B shows a victim 122 of cardiac arrest being cared for by a rescuer and a defibrillator 124. The defibrillator 124 includes an electrode package 126 and a compression puck 128 generally coupled thereto. An example of such a defibrillator includes the AED PLUS automated external defibrillator or the AED PRO automated external defibrillator, both from ZOLL Medical Corporation of Chelmsford, Ma. Other embodiments of the defibrillator 124 are possible.

In the pictured example, the victim 122 is rendered prone due to an arrhythmic episode, and the electrode package 126 and the compression puck 128 are positioned on the torso of the victim 122 in an appropriate and known arrangement. In accordance with the present disclosure, the defibrillator 124, in tandem with one or both of the electrode package 126 and the compression puck 128, is configured to determine whether a defibrillation shock will be an effective measure to terminate the arrhythmic episode. The determination is generally based on prior success or failure of defibrillating shocks, one or more trans-thoracic impedance measurements, and one or more calculated AMSA values. As shown in the figure, the patient 122 is shown at two points in time—(a) point t1 at which the patient has been defibrillated and is shown with his eyes open and a healthy ECG pattern 135A to indicate such successful defibrillation, and (b) at a later time t2, when the patient has refibrillated and is shown with closed eyes to represent such a state, and with an erratic ECG trace 135B.

The defibrillator 124 is configured to acquire and manipulate both a trans-thoracic impedance signal 130 and an ECG signal 132 via the electrode package. As described in further detail below, a trans-thoracic impedance measurement (□) is a parameter derived from the trans-thoracic impedance signal 130 that represents, among other things, thoracic fluid content. An AMSA value (V-Hz) is a parameter calculated by integrating the Fourier transform of the ECG signal 132 over a finite frequency range. The AMSA value is one form of calculation that represents a value of an ECG signal from a victim, while other SPA values may likewise be computed.

The defibrillator 124 is further configured to display an indicator 134A/B based on the defibrillating history (determined from ECG data), trans-thoracic impedance measurement(s) and AMSA value(s) obtained from the ECG signal 132, trans-thoracic impedance signal 130 and an ECG signal 132, respectively. The indicator 134A/B generally provides a perceptible cue that suggests whether or not a particular defibrillation event will likely terminate the arrhythmic episode of the victim 122. For example, for the victim 122 at time t1, the indicator 134A displays an X to indicate that no shock should be delivered to the victim 122. In contrast, at time t2, the indicator 134B displays a success indication of “88%,” so a rescuer (not shown) can be instructed “Press to Shock,” so as to apply a shock to the victim 122 via actuation of a control 137 (e.g., a button that the user can actuate).

In this situation, the indication of an 88% likelihood of success was made by consulting data structure 130, which may be stored in memory of defibrillator 124 upon analysis that occurred around the time of t1, and applying an appropriate calculation to data from the data structure 130. In particular, the defibrillator may analyze ECG data and an indicator provided by shock delivery circuitry in order to determine that a shock was delivered, and at a time soon after, the patient's heart rhythm entered a normal pattern, such that the defibrillator 123 may determine that the shock was a success at time t1. Upon making such a determination, the defibrillator may update data structure 130 to indicate that a successful defibrillation event has occurred during the rescue attempt. Other shocks may also be delivered, and the data structure 130 may be updated to reflect such events, and the success or failure of such events.

Data structure 130 or another data structure may also store information about prior AMSA readings for the victim during the particular VF episode. For example, a separate AMSA measurement and calculation may be made periodically (e.g., multiple times each second, once each second, or once every several seconds) and at least some past calculated AMSA values may be stored in data structure 130. Such values may be combined, and determinations may be made about general values (with low variability because of the combining) and trends in AMSA values, where such determination may indicate information such as the progress of the victim through phases that are generally indicative of the likelihood of success of particular actions taken on the victim by a rescuer. Moreover, such information may be used to generate an indication to a rescuer of the elapsed time (approximate) since the victim entered VF, or an indication of the phase the victim is currently in, among other things.

Embodiments other than those that display percentage likelihood for a shock indication are possible for the one likelihood indication discussed here. For example, it will be appreciated that a success indication may be implemented as any appropriate type of perceptible feedback (e.g., haptic, audio, etc.) as desired. Two simultaneous indications may also be provided, where both may be the same style of indication (e.g., visual display) or different types (e.g., visual display for one and haptic for the other)—e.g., the phase in which a victim is currently located may be displayed on a screen of a defibrillator, while a current AMSA value indicating a relatively high chance of success may be communicated by vibration of or display on a puck on which the rescuer has placed his hands (so as to encourage the rescuer to back-off and provide the shock).

In certain implementations, the defibrillator 124 may make the determination of a likelihood of success without expressly notifying the rescuer, and may simply use the determination to determine when to tell the rescuer that a shock may be delivered, or to provide other instructions to a rescuer. In other situations, the defibrillator 124 may explicitly indicate the likelihood of success, such as by showing a percentage likelihood, by showing less discrete gradiations for success (e.g., poor, good, very good, and excellent), or by displaying a range of colors (e.g., with red indicating a poor chance and green indicating a good chance). The type of indication that is displayed may also differ based on a mode in which the defibrillator 124 is operating—for example, in a professional mode, more detailed information may be provided, whereas in an AED mode, simpler information (a “go”/“no go” choice) may be presented.

In such manner then, the defibrillator may conduct a number of relatively complex calculations and may combine multiple factors in determining whether to allow a shock to be provided to a patient, or to encourage the application of such a shock by a rescuer.

FIG. 1C is a graph 130 that represents changes in AMSA during a VF event correlated to phases in the event. In general, the graph 130 shows how AMSA varies along with variations in a patient ECG, and varies more generally over a longer time period by falling over time after the event has started.

The time across this graph may be, for example, about 15 minutes. The time is broken into three phases. A defibrillation phase 133 may represent about the first 4 minutes (plus or minus one minute) of the event. A deep CPR phase 134 may run from about four minutes to about 10 minutes after onset of the event. And an Other CPR phase 136 may represent the remainder of the event, assuming the victim has not been revived by that time.

Line 138 is represented as being drawn through all of the AMSA values computed periodically throughout the time of the event. (The line is shown falling linearly here for clarity, though AMSA generally decreases exponentially. If AMSA were graphed for a rescuer, it could be shown as an exponential curve, as a line on an exponential scale, and/or with error bars showing statistical variation in the readings.) As can be seen, the AMSA values vary up and down (with a general downward trend over time), and such variation represents changes in the victim's ECG where the changes can represent changes in likelihood that a shock, currently delivered, will be successful. But although there is relatively large variation over short time periods, the variation is less over longer time windows, such as over 10 or more seconds. Thus, for example, AMSA values may be computed periodically over a short time period, and more general values may be computed by averaging or otherwise combining the individual measurements. A running average is represented by line 140. Line 140 may simply represent the average of past computations, and may also be extended into the future in certain implementations, such as by linear regression or other appropriate statistical techniques. For purposes of clarity, the overall AMSA value is shown here as falling linearly with time, though the actual variation may differ from what is shown here.

In this example, two points on line 140 are particularly relevant, points 142 and 144. These points represent locations at which the combined AMSA value measurement (e.g., averaged over a window of time) fall below a predetermined value. For example, the value for point 142 may have been selected from observations of ECG data, and corresponding AMSA values from data captured for actual real-world resuscitation events with real victims, and such data may indicate that resuscitation from shock falls below an acceptable value and/or falls off more quickly upon passing below a particular AMSA value. Such AMSA value may be selected as a cut-off point that defines the line between the first phase and the second phase. Similarly, such data may indicate that chest compressions or a particular type of chest compressions, such as forceful chest compressions, fell below a particular level of effectiveness or changed relatively rapidly in their effectiveness past another AMSA value. As such, point 144 may represent an AMSA value determined from such data analysis to correspond to such changes as observed across the large population of VF events. The points 142, 144 are mapped to the determined values with horizontal dotted lines, and a defibrillator or other device may monitor the combined AMSA value as an event progresses so as to identify when the predetermined AMSA value is reached. A similar monitoring may be employed with respect to identifying the existence of point 144.

Each of the points 142, 144 is also mapped to the time axis, representing the time at which the particular victim was determined to have transitioned from one phase to another. Generally, the times will be relatively similar as between different victims and different cardiac events, where the changes are driven in large part by ischemic effects that the event has on the heart tissue. At such points in time for the particular victim represented by this graph, the behavior of a medical device such as a defibrillator that is treating the victim may change in the ways discussed above and below.

As such, the device may determine an estimated time since the VF event began using AMSA values and/or other information, where particular AMSA values from a studied population have been determined to correspond to certain times since collapse or other instantiation of the VF event. Such information may be displayed in real-time or stored, such as to determine response times, and to perform studies on effectiveness of rescuers as a function of the time since initiation of the event when a defibrillator is first connected and operable for the victim.

Example A

As for particular AMSA values for use in defining points 142 and 144, one example may be instructive. Data from an Utstein-compliant registry along with electronic ECG records were collected on consecutive adult non-traumatic OHCA patients treated by 2 EMS agencies over a 2 year period. Patients with bystander witnessed CA and with VF as initial CA rhythm were included (n=41). AMSA was calculated in earliest pause without compression artifacts, using a 2 second ECG with a Tukey (0.2) FFT window. VF duration was calculated as the sum of the time interval from collapse to defibrillator on and the time interval from defibrillator on to first CPR interruption for defibrillation delivery.

VF duration ranged between 6.5 and 29.6 min (11.3+4.1 min), with a corresponding AMSA between 2.1 and 16.4 mV-Hz (9.4+4.2 mV-Hz). AMSA measured in the circulatory phase (N=19) was significantly higher than that in the metabolic phase (N=22) (8.14+3.17 vs. 5.98+2.88, p=0.03). Linear regression revealed that AMSA decreased in the analyzed population by 0.22 mV-Hz for every min of VF. AMSA was able to predict circulatory phase with an accuracy of 0.7 in ROC area. An AMSA threshold of 10 mV-Hz was able to predict the circulatory phase with sensitivity of 32%, specificity of 95%, PPV of 86%, NPV of 62%, and overall accuracy of 66%.

FIG. 1D is a table showing examples that relate AMSA to predicted likelihood of failure in defibrillating a victim who has or has not been previously defibrillated. The data was generally analyzed to determine the correlation between AMSA values and prior defibrillation success or failure with respect to success of subsequent defibrillation attempts.

The table shows the results of analysis of 1291 quality defibrillation events from 609 patients. AMSA was calculated for each such set of data based on a 1024 point ECG window that ended 0.5 seconds before each defibrillation. In the data, defibrillation was deemed successful when a spontaneous rhythm existed equal to or greater than 40 bpm and starting within 60 seconds from the shock, and also lasting for more than 30 seconds. A range of AMSA thresholds was calculated and evaluated for the data. The actual results shown in the other tables use the same or similar data.

In summary of the data, where no prior defibrillation had occurred, the mean AMSA for successful shocks was 16.8 mV-HZ, while the mean for unsuccessful shocks was 11.4 (p<0.0001). For subsequent shocks, the mean AMSA value fell to 15.0 for successful shocks and 7.4 for unsuccessful shocks.

Referring more specifically to the table itself, examples of data from defibrillation events were binned according to different AMSA values applied to the data as AMSA thresholds that would be used to determine whether to apply a subsequent shock. The first column of the table shows the different assigned AMSA values, while the second column shows the number of events that the particular chosen AMSA value correctly predicted, as compared to data indicating whether a defibrillation that was then applied was successful. The last column shows percentages with which the relevant AMSA value would have resulted in an accurate prediction if it had been used in the situations represented by the test data.

The upper section shows statistics for a first defibrillation attempt for each patient, while the lower section shows data for subsequent defibrillation attempts. The data indicates that lower AMSA values may provide more accurate predictions for subsequent defibrillations than for earlier defibrillations.

The upper portion of the table shows a comparison of aggregate mean AMSA values of first versus second shock, second versus third shock, etc. As the data indicates, such AMSA values generally fall from the first defibrillation attempt to the second, and to a lesser amount generally for each additional defibrillation attempt.

FIG. 1E is a schematic diagram of a data structure for correlating AMSA and prior defibrillation shocks to predicted outcomes for shocking a victim. The data structure here is greatly simplified in an effort to show how AMSA values and determinations about a number of prior shocks (successful or unsuccessful) may be used to predict whether another shock will succeed. This particular table shows correlations for prior shocks generally, though additional tables may be needed for identifying correlation for prior successful or unsuccessful shocks.

The table is shown in a format by which a program or human user could enter at one side of the table to select the value of one input variable, and then move across to the value of another variable, and obtain for an output a percentage likelihood of success. For example, the number of prior shocks are listed across the x-axis at the top of the table, while the percentage likelihood of success is shown along the right edge on the y-axis. The values in the body of the table are AMSA values that have been normalized to a 0 to 100 scale. The actual values are not intended to represent any actual outcome or actual numbers, but simply to indicate the interaction of the various values in coming to a conclusion about a likelihood of success.

Thus, for example, if a patient has received two defibrillating shocks, one would move to the third column of the table and then move down to a measured AMSA number—say 60. One would then move to the right edge to see the percentage likelihood of success—here, 70%. Values between those shown in the cells of the table can be rounded or interpolated or otherwise handled so as to provide likelihoods between each 10% value shown in the data structure.

The likelihood of success identified from the data structure may then be used in various ways to implement the likelihood determination, such as providing the number for the determined likelihood to a microprocessor that can use it to determine whether to enable the shocking capability of a defibrillator and/or to display the value or a related value on the defibrillator for review by a rescuer. Where additional factors (e.g., trans-thoracic impedance) are to be considered, the table may take on additional dimensions, multiple tables may be used, or other techniques for generating a likelihood that is a composite of multiple different factors may be used.

FIG. 1F is a table showing predictions of successful defibrillation for different AMSA threshold values for instances of first defibrillation attempts. The threshold values are listed in the first column, and the cells to the right of each AMSA value indicate particular outcomes for shocks delivered at those AMSA values for initial shocks.

The particular values shown include sensitivity, specificity, positive predictive value (PPV), negative predictive value (NPV), and accuracy, which are statistical measures of the performance of AMSA prediction for shock outcome. Sensitivity indicates the proportion of actual shock successes that were correctly identified. For example, if there were 100 shock successes, and 60 of the 100 were identified by an AMSA threshold of 10 mVHz, then the sensitivity is 0.6 using 10 mVHz as the AMSA threshold. Specificity represents the proportion of shock failures that were correctly identified by the particular AMSA value. PPV is the shock success rate. For example, if 10 mVHz was used as the AMSA threshold to deliver shocks and 100 shocks were delivered with 60 defibrillation successes, PPV=0.6. NPV is the shock failure rate. For example, if 10 mVHz was used as the AMSA threshold for the 100 cases, with AMSA <10 failing to shock, there are 90 cases of failed shock, or NPV=0.9. Accuracy is the proportion of true results (correctly predicted as shock success and shock failure by AMSA) in the total patient population.

FIG. 1G is a table showing AMSA prior defibrillation for refractory and recurrent VF. In particular, the table shows AMSA values that were measured before a defibrillating shock was delivered, and then correlated to whether the shock was successful or not. The first row shows the mean AMSA for all shocks, successful or unsuccessful, broken out by whether refractory VF was present or recurrent VF was present (where mean+/−SEM is shown for each of the values in the table). The second row shows the AMSA, for both refractory and recurrent VF, where the result of the shock was a successful defibrillation, while the third row shows corresponding values for shocks that did not successfully defibrillate. The final row shows the shocks that were successful in defibrillating the subject, both in terms of percentage and numbers. As can be seen, the level of success was much higher for recurrent VF than for refractory VF, and the AMSA was also higher.

FIG. 1H is a table showing prediction of successful defibrillation for increasing AMSA threshold values in the instances of refractory VF. The parameters shown in the table are similar to those shown for FIG. 1E.

FIG. 1I shows examples of window functions and resulting FFTs from those functions. As noted above, window widths in the time domain of less than 4 second down to about one second, less than three seconds down to about one second, and less than two seconds down to about one second, may be used. The figure shows, at the top, a boxcar window that is not tapered and thus may have negative transitory effects introduced into the FFT that it produces. The figure shows, at the bottom, a Tukey window, which is tapered as a sine wave, and is capped at a maximum value before coming down on the back side according to the falling value for the sine wave. The window thus lessens the effect of transients cause by the sudden switching of the boxcar window.

FIG. 1J shows ROC (receiver operating characteristic) Area values for five different window functions applied to a one second window of ECG data. In this example, digitalized ECG recordings were collected from multiple emergency medical services in the U.S. through a regular field case submission program. The sampling rate of all the ECG data files was 250 Hz. An episode of 1.025 seconds (256 data points, sample rate 250 Hz) waveform ending at 0.5 seconds before each shock attempt were selected for analysis. Five windowing functions were used for analysis. Shock success was defined as an organized rhythm that was present for a minimum of 30 seconds, starting within 60 seconds after the shock, and that had a rate of 40 beats per minute or greater.

Certain values shown in the figure have diagnostic value when used in combination with the methods discussed here. For example, when comparing one method of analysis to another, a “p-value” provides a measure of a difference between two groups of measurements, with lower p-values generally being better compared to higher p-values. By statistical convention, a value of p<0.05 is considered to be statistically significant. An Area Under the Curve (“AUC”) measures the area under the ROC curve. The “squarer” the ROC curve is, the greater the accuracy of the diagnostic in general; the AUC is greater for “squarer” curves. The Chi-square test is a simple statistical comparison of the probability distribution of two or more groups where the outcomes are binary.

A total of 1291 shocks (321 successful) from 609 patients with witnessed VF were included in the analysis. As shown in FIG. 1J, a Tukey window (R=0.2) resulted in significantly higher area under the ROC curve compared to other FFT windows.

Thus, as shown by this study, a defibrillator or other device as discussed above and below may be programmed to make AMSA determinations for purposes of predicting a likelihood of successful defibrillating shock using a Tukey window of a width of about 1 second. In other instances, it may be determined that one of the other three types of tapered windows is appropriate, or at least more appropriate than the non-tapered rectangular, or boxcar, window function. Similarly, multiple different window functions may be used for a particular patient, and an AMSA value may be generated from a combination of the different window function readings.

Each of these tables represent values that may be provided as parameters for the operation of a device that determines likelihood of success for a shock or provides other determinations for use in providing care to a patient suffering from VF. For example, the values determined from testing a large number of past events may be used as values that determine the likelihood values that a device correlates with a particular AMSA value at a particular time after VF starts. In this manner, then, data from observations of care provided to prior patients may be used to program a system for providing better case to future patients, particularly with respect to providing guidance on when a shock is likely to be successful in defibrillating the patient.

Referring now to FIG. 2 , a schematic block diagram 200 shows an example defibrillator 201, along with the example electrode package 102 and compression puck 104, of FIG. 1A in more detail. In general, the defibrillator 201, and optionally one or more of the electrode package 102 and compression puck 104, defines an apparatus for administering care to a patient, subject, or individual (e.g., victim 122) who requires cardiac assistance.

The defibrillator 201 includes a switch 202 and at least one capacitor 204 for selectively supplying or applying a shock to a subject. The defibrillator 201 further includes an ECG analyzer module 206, a trans-thoracic impedance module 208, a CPR feedback module 210 that controls frequency and magnitude of chest compressions applied to a subject, a patient treatment (PT) module 212 (which includes a defibrillation history analyzer 215), a speaker 214, and a display 216. In this example, the ECG analyzer module 206, trans-thoracic impedance module 208, CPR feedback module 210, and patient treatment (PT) module 212 are grouped together as a logical module 218, which may be implemented by one or more computer processors. For example, respective elements of the logical module 218 can be implemented as: (i) a sequence of computer implemented instructions executing on at least one computer processor of the defibrillator 201; and (ii) interconnected logic or hardware modules within the defibrillator 201, as described in further detail below in connection with FIG. 6 .

Similar to using individual AMSA values, multiple AMSA values may be used for making treatment determinations. For example, time series data of AMSA values, discernible trends of AMSA values, etc. may be used to define one or more conditions for which particular treatments, treatment adjustments, etc. should be employed. For example, AMSA time series data may be used for predicting the likelihood of successful defibrillation, indicating effective CPR, etc. Referring to FIG. 1L, a chart tabulates AMSA data from an investigation in which CPR was simulated by using extracorporeal circulation (ECC) on open-chest swine. During the investigation, VF was induced and each (of eight) swine were left untreated for eight minutes. After this eight-minute time period, the ECC was initiated and maintained for a ten minute period while the flow was adjusted to produce a coronary perfusion pressure (CPP) of 10 mmHg. After delivery of an initial defibrillation shock, the ECC flow was increased and titrated to secure a mean aortic pressure of 40 mmHg and additional electrical shocks were delivered at 60 second intervals. In this model, defibrillator shock success was defined as organized rhythm lasting more than 5 seconds. As represented in the chart, blood flow in the left anterior descending (LAD) coronary artery relative to baseline LAD blood flow was determined and represented as a quantity (identified as “LADrf”). Absent intervention, AMSA values generally decline in a progressive manner over time during VF. From collected data, based upon the completion of the ECC and prior to applying defibrillation shocks, the animals were assigned to one of two groups. In one group (represented in the chart of FIG. 1L as “Grp 1” and of which four animals were assigned), there was no change or a decrease in AMSA values (i.e., change in mean value being −1.1±1.2) over the time period of the start of ECC to end of ECC. For the second group (represented in FIG. 1L as “Grp 2”), which contained the remaining four animals, the data reported an increase in AMSA values (i.e., change in mean being +3.7±2.7) with all animals showing a progressive increase in AMSA over the period of start of ECC to end of ECC. Regarding the LADrf flow just prior to first shock being administered, the flow trended higher for the Group 2 animals, compared to the Group 1 animals. As such, the AMSA values and the LADrf flow quantities collected from the Group 2 animals have larger and thereby better levels than the corresponding quantities of the Group 1 animals. The chart also reports, for each group, the period of time to a successful defibrillation shock. In particular, less time is needed for the Group 2 animals to achieve a successful first shock (e.g., approximately 721 seconds for Group 2 versus 837 seconds for Group 1).

Based upon these quantities, in particular the AMSA values, the Group 2 animals have a better predicted likelihood of shock success compared to the Group 1 animals, which generally need a longer period of time to achieve a successful first shock. As such, from the chart data, AMSA values (calculated prior to defibrillation), temporal trends in the data, etc. can be used for treatment determinations. For example, for relatively flat or decreasing trends in AMSA values, CPR efforts may be recommended until the AMSA values change (e.g., increase, a positive trend is measured, etc.). Translated into clinical terms, if CPR is being performed on a patient and the AMSA values increase to show a positive trend, the likelihood of a successful shock can be considered higher than if it were a trend of little or no change, i.e. insignificant change, or a decreasing trend. For instance, the series of transform values, such as AMSA may be considered to have a trend of insignificant change (or a decreasing trend) if AMSA increases by less than 10% over the course of one minute of resuscitation treatment. Statistical analyses such as control charts, change point analysis, or other time series analyses may be employed to determine whether the series of transform values changes over a period of time to a threshold degree. Alternatively, the shape of the transform value trend can also be analyzed to determine if AMSA has stopped increasing, and/or is substantially flat. In some implementations, at the time when AMSA is at a maximum (or within a predetermined range of the maximum), but before being at the maximum (or within the predetermined range) for more than a threshold amount of time (e.g., 30 seconds), it may be desirable to deliver a shock. In some implementations, it could be desirable to deliver a shock before the transform value starts to decay. This may be indicated, for example, in the shape analysis of the trend as a zero-crossing of the first derivative (or the second derivative exceeding a negative value above a threshold). However, if the AMSA values remain relatively flat (or decrease) as CPR is being performed, the rescuer may need to continue chest compressions, provide a pharmacologic agent (i.e., epinephrine) to increase central blood pressures, change their chest compression technique (e.g., perform deeper compressions, compressions of faster rate, etc.), or perform another intervention technique to increase the AMSA values (and correspondingly increase the likelihood of a successful shock).

Similar to using AMSA values for estimating likelihood of defibrillation success, quantities calculated from AMSA values may be used for treatment determinations. Trending of AMSA values may be quantified (e.g., by differentiating portions of AMSA value time series), data may be normalized, weighting may be applied, various operations applied to the AMSA values, etc. to determine the likelihood of success or other quantities. In analyzing trends of AMSA values, the actual AMSA values (e.g., initial value) can factor in treatment determinations. For example, an AMSA value of 15.0 can be considered appropriate (e.g., large enough) to indicate a good likelihood of defibrillation success. Correspondingly, values near 15.0 can also be considered a good indication of a likelihood of defibrillation success. So even if a flat trend or a minimal positive trend is detected (e.g., AMSA values over time remain constant at 15.0 or only slightly increase to 16.0), the actual AMSA value (e.g., 15.0 or slightly larger) can govern and a good likelihood of a successful shock can be reported by the defibrillator. Alternatively for lower AMSA values, data trending may be heavily weighted. For example, due to CPR being applied a patient's AMSA value may significantly change from 5.0 to 12.0. Based upon such a positive trend in the AMSA values, a determination may report that the likelihood of shock success has increased and defibrillation may be administered.

To present the AMSA values, trend data, etc. (e.g., represented in the chart) to a rescuer or other individual, one or more techniques may be utilized. A graphical display incorporated into a defibrillator (such as the defibrillators described above and below) may present individual AMSA values, time averaged values, etc. in near real time to provide a numerical quantity of the patient's condition and the likelihood of defibrillation success (e.g., a value of “5.0 AMSA” can be considered as a value with a low likelihood of success while a value of “15.0 AMSA” can be considered as representing a relatively high likelihood of success). Graphical representations may also be employed to present the trending of the AMSA time series data. Positive trending values may be graphically represented in one color (e.g., blue) while relatively flat or negative trending AMSA values may be representing in another eye-catching color (e.g., red). Provided such image cues, rescuers can quickly determine if CPR efforts should continue (since a high likelihood of defibrillation success has not been reached), if CPR efforts should be adjusted (e.g., adjust to deeper and faster compressions based upon negatively trending AMSA values), if CPR can be halted for applying a defibrillation shock, etc. A threshold may be set for desired improvement in AMSA

Similar to graphical representations, other types of representations (e.g., audio alerts, guidance messages, etc.) may be employed by a defibrillator (or other type of computing device) to support the use of AMSA values prior to defibrillation and the use of its trends during CPR as a useful tool to determine the quality of the CPR being provided and the likelihood of defibrillation success.

Similar to determining the likelihood of defibrillation success, AMSA values may be used to make other determinations such as classifying cardiac rhythm in VF or in asystole, a state of no cardiac electrical activity, as well as identifying treatments for patients classified in VF or in asystole. For example, based upon a threshold defined by an AMSA value, a patient may be identified as being in VF or in a state of no cardiac electrical activity referred to as asystole (colloquially known as flatline). Generally, CPR should be employed (or continued) if a patient is asystolic since shock treatment may not improve the patient's condition and in some situations can worsen their condition. One study has demonstrated that asystole following defibrillation can produce a worse prognosis than primary asystole or pulseless electrical activity (PEA). By investigating the relationship between pre-shock AMSA values and the appearance of post-shock asystole, one or more determination techniques can be identified for either applying a shock or initiating (or continuing) a non-shock treatment such as administering CPR.

In one investigation, ECG recordings, sampled at 250 Hz, were digitized and data associated with initial shocks at a particular energy level (i.e., 120 Joules) was reviewed. Episodes of approximately two seconds (e.g., 2.05 seconds or 512 data points) that terminated a half second before a shock attempt were analyzed for AMSA values. As illustrated by a chart shown in FIG. 1K, post shock rhythms were annotated as VF, asystole, PEA or tROSC (i.e., an organized rhythm present for a minimum of 30 seconds, started within 60 seconds after that shock, and having a rate of 40 beats per minute or larger). Data from a total of 543 patients with VF was investigated. From the data, for AMSA values of 3 mV-Hz or less, defibrillation resulted in 77.8% post-shock asystole and 22.2% of other non-perfusing rhythms (with no instances of tROSC). As illustrated in the figure, for AMSA values larger than 3.0 mV-Hz, asystole levels reported considerable decreases along with corresponding increases in post-shock VF, PEA and tROSC.

One or more conditions may be predefined for determining whether a defibrillation shock should be initiated for treatment. For example, an initial AMSA value can be determined from a patient's ECG, and then the measured AMSA value can be compared to a threshold value (e.g., an AMSA value of 3 mV-Hz). For measured values equivalent to or exceeding the threshold, defibrillation treatment may be deemed appropriate and initiated. For measured values below the threshold (e.g., below 3 mV-Hz), asystole as a predominate post-shock rhythm can be considered probable and rhythm restoration by defibrillation may prove futile. As such, another recommended treatment such as CPR would be initiated or continued (if previously initiated).

Such determinations may be executed by one or multiple system components, for example, the AMSA analyzer 108 (shown in FIG. 1A) may utilize data from the ECG unit 106 (which may be part of a portable defibrillator) to determine if a predefined threshold (e.g., an AMSA value of 3 mV-Hz) has been met or exceeded. System equipment, modules, etc. described above and below may assist in determining and utilizing this information; for example, equipment may be used to deliver a defibrillating shock to a patient if a determined AMSA value (measure from the patient's ECG data) exceeds the predefined AMSA threshold. Along with different AMSA values (e.g., larger or smaller than 3 mV-Hz) being used for such determinations, other processing techniques may be employed. For example, multiple values (e.g., current and previous AMSA values) may be employed such that historical trends (hysteresis) factor into VF determinations and whether to use defibrillation or continue CPR.

In the example of FIG. 2 , the electrode package 102 is connected to the switch 202 via port on the defibrillator 201 so that different packages may be connected at different times. The electrode package 102 may also be connected through the port to ECG analyzer module 206, and trans-thoracic impedance module 208.

The compression puck 104 is connected, in this example, to the CPR feedback module 210. In one embodiment, the ECG analyzer module 206 is a component that receives an ECG (e.g., ECG signal 132). Similarly, the trans-thoracic impedance module 208 is a component that receives transthoracic impedance (e.g., trans-thoracic impedance signal 110). Other embodiments are also possible.

The patient treatment module 212 is configured to receive an input from each one of the ECG analyzer module 206, trans-thoracic impedance module 208, and CPR feedback module 210. The patient treatment module 212 uses inputs as received from at least the ECG analyzer module 206 and trans-thoracic impedance module 208 to predict whether a defibrillation event will likely terminate an arrhythmic episode. For example, ECG data can be used both to determine AMSA values for a patient, and also determine whether shocks are effective or not so that such information can be saved and used to identify likelihoods that subsequent shocks will be effective). In this manner, the patient treatment module 212 uses information derived from both an ECG signal (both for AMSA and for adjusting the AMSA value) and transthoracic impedance measurement to provide a determination of a likelihood of success for delivering a defibrillating shock to a subject.

The patient treatment module 212 is further configured to provide an input to each one of the speaker 214, display 216, and switch 202. In general, input provided to the speaker 214 and a display 216 corresponds to either a success indication or a failure indication regarding the likelihood of success for delivering a shock to the subject. In one embodiment, the difference between a success indication and a failure indication is binary and based on a threshold. For example, a success indication may be relayed to the display 216 when the chances corresponding to a successful defibrillation event is greater than 75%. In this example, the value “75%” may be rendered on the display 216 indicating a positive likelihood of success. When a positive likelihood of success is indicated, the patient treatment module 212 enables the switch 202 such that a shock may be delivered to a subject.

The patient treatment module 212 may also implement an ECG analyzer for generating an indication of heart rate for the patent, for generating an indication of heart rate variability for the patent, an indication of ECG amplitude for the patent, and/or an indication of a first or second derivative of ECG amplitude for the patient. The indication of ECG amplitude can include an RMS measurement, measured peak-to-peak, peak-to-trough, or an average of peak-to-peak or peak-to-trough over a specified interval. Such indications obtained by the ECG analyzer may be provided to compute an AMSA value for the patient and/or can be used in combination with a computed AMSA value so as to generate some derivative indication regarding whether a subsequent shock is likely or unlikely to be effective (and the degree, e.g., along a percentage scale, of the likelihood).

In another embodiment, likelihood of a successful defibrillation event may be classified into one of many possible groups such as, for example, low, medium, and high likelihood of success. With a “low” likelihood of success (e.g., corresponding to a successful defibrillation event is less than 50%), the patient treatment module 212 disables the switch 202 such that a shock cannot be delivered to a subject. With a “medium” likelihood of success (e.g., corresponding to a successful defibrillation event is greater than 50% but less than 75%), the patient treatment module 212 enables the switch 202 such that a shock may be delivered to a subject, but also renders a warning on the display 216 that the likelihood of success is questionable. With a “high” likelihood of success (e.g., corresponding to a successful defibrillation event is greater than or equal to 75%), the patient treatment module 212 enables the switch 202 such that a shock may be delivered to a subject, and also renders a cue on the display 216 indicating that the likelihood of success is very good. Still other embodiments are possible.

Thus, the system 200 may provide, in a portable electric device (e.g., a battery-operated device) the capability to analyze a number of inputs and to identify a variety of factors from those inputs, where the factors can then be combined to provide a flexible, intelligent determination of likely success.

Referring now to FIG. 3A, an example method 300 is shown for administering care to an individual requiring cardiac assistance. In one embodiment, the method 300 is implemented by the example defibrillators described above in connection with FIGS. 1B and 2 . However, other embodiments are possible.

At a step 302, at least one of an ECG signal (e.g., ECG signal 132) and a trans-thoracic impedance signal (e.g., trans-thoracic impedance signal 110) of the subject receiving cardiac care is monitored. In general, an individual receiving cardiac care includes the individual at any time during a cardiac event, including whether or not individual is receiving active care (e.g., chest compressions).

At a step 304, a trans-thoracic impedance value is extracted from the trans-thoracic impedance signal as monitored at step 302. Additionally, at step 304, an AMSA value can be calculated from the ECG signal as monitored at step 302 by integrating the Fourier transform (e.g., FFT) of the ECG signal over a finite frequency range. Example frequency content of an arrhythmic ECG signal generally ranges between about 1 Hz to about 40 Hz, with amplitude of about 50 mV or less. An example of an AMSA value calculated from such a signal ranges between about 5 mV-Hz to about 20 mV-Hz. It will be appreciated however that this is only an example, and that the magnitude and spectra of an ECG signal ranges greatly.

The AMSA value may be determined from a moving window that moves in time through the incoming ECG data as it arrives (e.g., the raw ECG data may be cached for a period at least as long as the window), where the window may be about one second wide (or more), and can be measured multiple times each second so that there are overlapping windows. The window may also have a tapered (rather than rectangular) window function so as to improve the accuracy of the AMSA value in predicting defibrillation success. Furthermore, the coefficients for the window may be selected to maximize the predictive ability of the system. In addition, multiple different AMSA values may be determined (e.g., with different window size, type, and/or coefficients) and a most-accurate AMSA may be determined and used to make a prediction, or a composite value may be generated from each of the determined AMSA values.

Additionally, the window size, type, and coefficients can change over time to allow a system to dynamically adjust to a particular VF event. For example, using determinations about the phase in which a VF event is, a system may change such parameters to switch to a window that is determined to better predict defibrillation success. Alternatively, a blend of window techniques may be used and the blend may change over time, while a composite prediction score is determined from the blended techniques.

For example, a system could shift from a symmetric window to an asymmetric window just prior to the end of a CPR interval as it gets closer to the time of a shock. The system may be continuously executing a noise detection process, and if sections of the data in the window are found to have ECG with anomalously high amounts of higher frequency noise compared to ECG in adjacent sections, then those portions of the window can be attenuated via adjusting the window characteristics. If the burst of noise occurs in the middle of the window, then the window function can be composed of two adjacent Tukey or other windows where the null of the superimposed windows is centered at the occurrence of the noise burst. Thus, various dynamic changes may be made to the window as the process occurs so as to adjust to particular activities for a patient.

At a step 306, the process identifies success levels of prior shocks applied to the patient during the cardiac event. Such determination may occur in various manners. At a simplest level, the process may simply track the number of times a defibrillating shock has been provided to the patient. In more complex implementations, the process may identify how many attempts were successful and how many were not, and in a slightly more complex implementation, may identify which were successful and which were not (e.g., because subsequent steps may perform more accurately by weighting the influence of different ones of the prior defibrillations in different ways). In yet more complex systems, the degrees of prior success can be determined, which may include determining how close the patient's defibrillated heart rate was to a predetermined rate (either a particular rate or a range of rates) or how consistent the rate was over time, or a combination of both to generate a score for the quality of the defibrillation. Other examples of physiologic measure that may be useful for generating a score may be pulse oximetry, capnography, blood pressure, or other pulse or blood flow detection methods.

As one such example, scoring the ECG quality of the post-shock ECG rhythm may occur by giving heart rates in the range of 50-90 BPM a higher score than those above or below that range (with the score decreasing the further from that range the heart rates were). More complex scoring systems could additionally or alternatively be used, such as using a windowing function that weights a heart rate of a patient to generate a normalized score. Such a windowing functions might be a Hamming window or a Tukey window with a rectangle width that is flat from 50-90 BPM. In each such situation, the data gathered for each defibrillation may be saved so that it can be accessed in preparation for determining and providing identifications of likely success for later defibrillations.

At step 308, the process determines a combined indicator of success that includes an indication from trans-thoracic impedance and an indication from an ECG reading, such as an AMSA indication, and is modified appropriately to reflect data about prior successes or failure in defibrillation. The combined indicator may be determined by inputting a trans-thoracic impedance value, an AMSA value, and a count or other indicator of prior success or failure, into a function or look-up table, or may be determined without a need to compute both or all values first, such as by taking inputs indicative of all values and computing a predictor of success directly from such indicative values. Alternatively to using a table to calculate the predictive score, the use of logistic regression may be used with a logistic regression equation, with inputs to the equation with, e.g. ECG rhythm type, ECG rate, transthoracic impedance, prior shocks, etc. Neural network or fuzzy logic methods or other non-linear decision-making methods may also be used. In certain instances, a single value, like AMSA may be used to compute the likelihood of success.

At box 310, a success indication is provided to a defibrillator operator. The indication may take a variety of forms. For example, the ability of the defibrillator to deliver a shock may be enabled when the indicator of success is higher than a threshold level, so that the success indicator is delivered by the operator being shown that a shock can or cannot be delivered. Also, the operator may be notified that the defibrillator can provide a shock, and may be prompted to push a physical button to cause the shock to be delivered.

In some implementations, the operator may also be provided with more detail about the success indication. For example, the operator may be shown a percentage number that indicates a likelihood in percent that the shock will be successful. Alternatively, or in addition, the operator may be shown a less granular level of an indication, such as a value of “excellent,” “good,” and “poor” to indicate to the operator what the likelihood of successful defibrillation is.

At box 312, the trigger mechanism is enabled on the defibrillator, as discussed above. In certain instances, such a feature may be enabled whenever a shockable rhythm is observed for a patient. In other circumstances, the enabling may occur only when the combined indication discussed above exceeds a threshold value for indicating that a shock will be successful in defibrillating the patient. For a hybrid defibrillator that is capable of manual and AED modes, the trigger mechanism may operate different depending on what mode the defibrillator is in.

An arrow is shown returning to the top of the process to indicate that the process here is in ways continuous and in ways repeated. In particular, ECG signals are gathered continuously, as are other types of data. And the process repeatedly tries to identify whether a shock can or should be provided, and the order and timing of the steps in that cycling may be dictated by standards as adjusted by a medical director or other appropriate individual responsible for the deployed defibrillator. Thus, for instance, the entire process may be repeated, certain portions may be repeated more frequently than others, and certain portions may be performed once, while others are repeated.

FIG. 3B is a flow chart of a process 320 for identifying a phase in a cardiac event so as to provide guidance to a rescuer. In general, the process involves using AMSA or other determinations to identify a length of time since a cardiac event has begun and/or a phase in which the event is currently located, where different phases are delineated by the relative likelihood of certain treatment approaches operating successfully vis-à-vis other phases.

The process 320 in this example begins at box 322, where a patient is monitored generally, such as by monitoring the patient's pulse and ECG, among other things. Such monitoring may be the same monitoring as in step 302 in FIG. 3A or may occur concurrently with such monitoring. The monitoring may constitute constantly receiving ECG data and periodically computing (e.g., every second or every two seconds) AMSA and other values from it. At the same time, an ECG representation may be displayed to an operator of a defibrillator or other medical device.

At box 324, the AMSA is determined, and may be calculated in known manners from the ECG data. Other SPAs may also be operated on the incoming data from the patient. As discussed above, the AMSA value may depend on a window function of a certain determined length and type, and having certain determined coefficients, where each of these parameters may be adjusted dynamically over the time of a VF incident.

At box 326, prior AMSA measurements are identified. Such a step may occur simply by looking to a known location in memory where a software program has been programmed to store such information. Those measurements or computations may be loaded to a location at which they can be manipulated relative to each other, including by combining those separate measurements into a composite, such as an average of the measurements. In obtaining such measurements, the process may fetch only n number of prior measurements with each cycle of the process, so that a rolling or sliding average is computed at each step. The number of values to combine in any given cycle can be selected so as to provide sufficient responsiveness (fewer readings) while providing a sufficient general view of the status of the patient that is not subject to extreme fluctuations (more readings).

At box 328, the current general AMSA level (e.g., from an average of multiple prior readings) is determined. Other measures of a similar type may also or alternatively be generated, if they represent the progression of the patient through nonrecurring phases of a cardiac event, such as those discussed above.

At box 330, the phase in the progression of the VF event is determined for the patient. Such a determination may include simply estimating, with the AMSA level or other such data, the time since the patient entered cardiac arrest, and/or more generally whether the patient is in electrical, circulatory, or metabolic phase. For example, the AMSA level for the patient may be provided to a look-up table that maps observed AMSA values for a population to event phases or time since the event started, or both.

At box 332, the process provides an indication of care that is correlated to the phase of the event. For example, a screen on a defibrillator may show a message indicating that the rescuer should prepare to administer a shock (e.g., if the patient is in electrical phase and the AMSA determination shows a high likelihood that the shock will be successful). Similarly, color may be used to show one or more of the parameters, such as a single color bar to show likelihood of shock success, where the likelihood is based on current AMSA, combined AMSA values (e.g., an average or trend), or a combination of both.

FIG. 4A shows a plot of positive predictive value (%) versus AMSA threshold (mv-Hz) for a first set of subjects having a trans-thoracic impedance measured greater than 150 ohms and a second set of subjects having a trans-thoracic impedance measured less than 150 ohms. As shown by the comparative data, the first set of subjects generally has a greater positive predictive value for a given AMSA threshold. In both cases, positive predictive value generally increases with increasing AMSA threshold. Thus, an indication of success for a patient having a low impedance may be provided when the AMSA value is lower, than for a comparable AMSA value from a high impedance patient. Or, where a percentage likelihood of success is shown, the displayed percentage for a particular AMSA value may be higher for a low impedance patient as compared to a high impedance patient—at least with the range of AMSA values from 5-20 mv-HZ.

FIG. 4B shows a plot of sensitivity (unit-less) versus AMSA threshold (mv-Hz) for a first set of subjects having a trans-thoracic impedance measured less than 100 ohms, a second set of subjects having a trans-thoracic impedance measured between 125 ohms and 150 ohms, and a third set of subjects having a trans-thoracic impedance measured between 150 ohms and 180 ohms. As shown by the comparative data, AMSA threshold generally increases, for a given specificity, with increasing trans-thoracic impedance.

FIG. 5A shows a defibrillator showing certain types of information that can be displayed to a rescuer. In the figure, a defibrillation device 500 with a display portion 502 provides information about patient status and CPR administration quality during the use of the defibrillator device. As shown on display 502, during the administration of chest compressions, the device 500 displays information about the chest compressions in box 514 on the same display as is displayed a filtered ECG waveform 510 and a CO2 waveform 512 (alternatively, an SpO2 waveform can be displayed).

During chest compressions, the ECG waveform is generated by gathering ECG data points and accelerometer readings, and filtering the motion-induced (e.g., CPR-induced) noise out of the ECG waveform. Measurement of velocity or acceleration of chest compression during chest compressions can be performed according to the techniques taught by U.S. Pat. No. 7,220,335, titled “Method and Apparatus for Enhancement of Chest Compressions During Chest Compressions,” the contents of which are hereby incorporated by reference in their entirety.

Displaying the filtered ECG waveform helps a rescuer reduce interruptions in CPR because the displayed waveform is easier for the rescuer to decipher. If the ECG waveform is not filtered, artifacts from manual chest compressions can make it difficult to discern the presence of an organized heart rhythm unless compressions are halted. Filtering out these artifacts can allow rescuers to view the underlying rhythm without stopping chest compressions.

The CPR information in box 514 is automatically displayed when compressions are detected by a defibrillator. The information about the chest compressions that is displayed in box 514 includes rate 518 (e.g., number of compressions per minute) and depth 516 (e.g., depth of compressions in inches or millimeters). The rate and depth of compressions can be determined by analyzing accelerometer readings. Displaying the actual rate and depth data (in addition to, or instead of, an indication of whether the values are within or outside of an acceptable range) can also provide useful feedback to the rescuer. For example, if an acceptable range for chest compression depth is 1.5 to 2 inches, providing the rescuer with an indication that his/her compressions are only 0.5 inches can allow the rescuer to determine how to correctly modify his/her administration of the chest compressions (e.g., he or she can know how much to increase effort, and not merely that effort should be increased some unknown amount).

The information about the chest compressions that is displayed in box 514 also includes a perfusion performance indicator (PPI) 520. The PPI 520 is a shape (e.g., a diamond) with the amount of fill that is in the shape differing over time to provide feedback about both the rate and depth of the compressions. When CPR is being performed adequately, for example, at a rate of about 100 compressions per minute (CPM) with the depth of each compression greater than 1.5 inches, the entire indicator will be filled. As the rate and/or depth decreases below acceptable limits, the amount of fill lessens. The PPI 520 provides a visual indication of the quality of the CPR such that the rescuer can aim to keep the PPI 520 completely filled.

As shown in display 500, the filtered ECG waveform 510 is a full-length waveform that fills the entire span of the display device, while the second waveform (e.g., the CO2 waveform 512) is a partial-length waveform and fills only a portion of the display. A portion of the display beside the second waveform provides the CPR information in box 514. For example, the display splits the horizontal area for the second waveform in half, displaying waveform 512 on left, and CPR information on the right in box 514.

The data displayed to the rescuer can change based on the actions of the rescuer. For example, the data displayed can change based on whether the rescuer is currently administering CPR chest compressions to the patient. Additionally, the ECG data displayed to the user can change based on the detection of CPR chest compressions. For example, an adaptive filter can automatically turn ON or OFF based on detection of whether CPR is currently being performed. When the filter is on (during chest compressions), the filtered ECG data is displayed and when the filter is off (during periods when chest compressions are not being administered), unfiltered ECG data is displayed. An indication of whether the filtered or unfiltered ECG data is displayed can be included with the waveform.

Also shown on the display is a reminder 521 regarding “release” in performing chest compression. Specifically, a fatigued rescuer may begin leaning forward on the chest of a victim and not release pressure on the sternum of the victim at the top of each compression. This can reduce the perfusion and circulation accomplished by the chest compressions. The reminder 521 can be displayed when the system recognizes that release is not being achieved (e.g., signals from an accelerometer show an “end” to the compression cycle that is flat and thus indicates that the rescuer is staying on the sternum to an unnecessary degree). Such a reminder can be coordinated with other feedback as well, and can be presented in an appropriate manner to get the rescuer's attention. The visual indication may be accompanied by additional visual feedback near the rescuer's hands, and by a spoken or tonal audible feedback, including a sound that differs sufficiently from other audible feedback so that the rescuer will understand that release (or more specifically, lack of release) is the target of the feedback.

FIG. 5B shows the same defibrillator, but with an indicator box 522 now shown across the bottom half of the display and over the top of information that was previously displayed to display a success indication of “75%.” Similar to the display 216 as described above, the indicator box 522 can generally convey a success indication or a failure indication regarding the likelihood of success for delivering a shock to a subject. The success indication can be generated using any combination of the techniques discussed above, including AMSA values, measures of prior effectiveness or ineffectiveness of prior defibrillating shocks, and trans-thoracic impedance.

In certain instances, one or more of the inputs used for determining a likelihood that a future shock will be successful, will not be available. For example, at times it may not be possible to calculate AMSA accurately when CPR compressions are occurring. Or perhaps a system is receiving values for trans-thoracic impedance that are not possible, which would indicate a problem with the sensors measuring such impedance or other similar problems. In such situations, the score that is generated to indicate a likelihood of success may be switched to a score that depends only on n−1 inputs (where n is the optimal number of inputs, and n−1 represents the removal of one of the inputs). Thus, the system may be adaptive to problems with particular ones of the inputs that indicate a likelihood of success, yet the system may still determine a likelihood of success that is as accurate as possible given the inputs that are available.

In the example shown, the success indication is textual; however the success indication (and/or failure indication) can generally be implemented as any type of perceptible feedback. For example, tone, color, and/or other perceptible visual effects can be rendered or otherwise displayed to a user via the indicator box. For example, the characters “75%” may be highlighted or otherwise distinguished in a bold color, and the phrase “Press to Shock” may blink at least intermittently to convey a sense of urgency with respect to a pending shock. Other embodiments are possible.

FIGS. 6A-6C show example screens that may be displayed to a rescuer on a defibrillator. Each of the displays may be supplemented with an indicator-like box 522 in FIG. 5B when the defibrillator makes a determination as to the likelihood of success for delivering a shock to a subject.

FIG. 6A shows exemplary information displayed during the administration of CPR chest compressions, while FIGS. 6B and 6C show exemplary information displayed when CPR chest compressions are not being sensed by the defibrillator. The defibrillator automatically switches the information presented based on whether chest compressions are detected. An exemplary modification of the information presented on the display can include automatically switching one or more waveforms that the defibrillator displays. In one example, the type of measurement displayed can be modified based on the presence or absence of chest compressions. For example, CO2 or depth of chest compressions may be displayed (e.g., a CO2 waveform 620 is displayed in FIG. 6A) during CPR administration, and upon detection of the cessation of chest compressions, the waveform can be switched to display an SpO2 or pulse waveform (e.g., an SpO2 waveform 622 is displayed in FIG. 6B).

Another exemplary modification of the information presented on the display can include automatically adding/removing the CPR information from the display upon detection of the presence or absence of chest compressions. As shown in FIG. 6A, when chest compressions are detected, a portion 624 of the display includes information about the CPR such as depth 626, rate 628, and PPI 630. As shown in FIG. 6B, when CPR is halted and the system detects the absence of CPR chest compressions, the defibrillator changes the CPR information in the portion 624 of the display, to include an indication 632 that the rescuer should resume CPR, and an indication 634 of the idle time since chest compressions were last detected. In a similar manner, when the defibrillator determines that rescuers should change, the label 632 can change to a message such as “Change Who is Administering CPR.” In other examples, as shown in FIG. 6C, when CPR is halted, the defibrillation device can remove the portion of the display 624 previously showing CPR data and can display a full view of the second waveform. Additionally, information about the idle time 636 can be presented on another portion of the display.

FIGS. 7A and 7B show defibrillator displays that indicate to a rescuer levels of perfusion being obtained by chest compressions that the rescuer is performing. FIG. 7A shows exemplary data displayed during the administration of CPR chest compressions when the CPR quality is within acceptable ranges, while FIG. 7B shows modifications to the display when the CPR quality is outside of the acceptable range.

In the example shown in FIG. 7B, the rate of chest compressions has dropped from 154 compressions per minute (FIG. 7A) to 88 compressions per minute. The defibrillator device determines that the compression rate of 88 compressions per minute is below the acceptable range of greater than 100 compressions per minute. In order to alert the user that the compression rate has fallen below the acceptable range, the defibrillator device provides a visual indication 718 to emphasize the rate information. In this example, the visual indication 718 is a highlighting of the rate information. Similar visual indications can be provided based on depth measurements when the depth of the compressions is shallower or deeper than an acceptable range of depths. Also, when the change in rate or depth indicates that a rescuer is becoming fatigued, the system may display a message to switch who is performing the chest compressions, and may also emit aural or haptic feedback to the same effect.

In the examples shown in FIGS. 7A and 7B, a perfusion performance indicator (PPI) 716 provides additional information about the quality of chest compressions during CPR. The PPI 716 includes a shape (e.g., a diamond) with the amount of fill in the shape differing based on the measured rate and depth of the compressions. In FIG. 7A, the depth and rate fall within the acceptable ranges (e.g., at least 100 compressions/minute (CPM) and the depth of each compression is greater than 1.5 inches) so the PPI indicator 716 a shows a fully filled shape. In contrast, in FIG. 7B, when the rate has fallen below the acceptable range, the amount of fill in the indicator 716 b is lessened such that only a portion of the indicator is filled. The partially filled PPI 716 b provides a visual indication of the quality of the CPR is below an acceptable range.

As noted above with respect to FIG. 5A, in addition to measuring information about the rate and depth of CPR chest compressions, in some examples the defibrillator provides information about whether the rescuer is fully releasing his/her hands at the end of a chest compression. For example, as a rescuer tires, the rescuer may begin leaning on the victim between chest compressions such that the chest cavity is not able to fully expand at the end of a compression. If the rescuer does not fully release between chest compressions the quality of the CPR can diminish. As such, providing a visual or audio indication to the user when the user does not fully release can be beneficial. In addition, such factors may be included in a determination of whether the rescuer's performance has deteriorated to a level that the rescuer should be instructed to permit someone else perform the chest compressions, and such information may be conveyed in the various manners discussed above.

As shown in FIG. 8A, a visual representation of CPR quality can include an indicator of CPR compression depth such as a CPR depth meter 820. The CPR depth meter 820 can be automatically displayed upon detection of CPR chest compressions.

On the CPR depth meter 820, depth bars 828 visually indicate the depth of the administered CPR compressions relative to a target depth 824. As such, the relative location of the depth bars 828 in relation to the target depth 824 can serve as a guide to a rescuer for controlling the depth of CPR compressions. For example, depth bars 828 located in a region 822 above the target depth bar 824 indicate that the compressions were shallower than the target depth, and depth bars 828 located in a region 826 below the target depth bar 824 indicate that the compressions were deeper than the target depth. Again, then depth is inadequate (along with perhaps other factors) for a sufficient time to indicate that the rescuer is fatiguing, an indicator to switch rescuers may be provided in the manners discussed above.

While the example shown in FIG. 8A displayed the target depth 824 as a single bar, in some additional examples, the target depth can be displayed as a range of preferred depths. For example, two bars 829 a and 829 b can be included on the depth meter 820 providing an acceptable range of compression depths (e.g., as shown in FIG. 8B). Additionally, in some examples, compressions that have depths outside of an acceptable range can be highlighted in a different color than compressions that have depths within the acceptable range of compression depths.

The depth bars 828 displayed on the CPR depth meter 820 can represent the compression depths of the most recent CPR compressions administered by the rescuer. For example, the CPR depth meter 820 can display depth bars 828 for the most recent 10-20 CPR compressions (e.g., the most recent 10 CPR compressions, the most recent 15 compressions, the most recent 20 CPR compressions). In another example, CPR depth meter 820 can display depth bars 828 for CPR compressions administered during a particular time interval (e.g., the previous 10 seconds, the previous 20 seconds).

In some additional embodiments, physiological information (e.g., physiological information such as end-tidal CO2 information, arterial pressure information, volumetric CO2, pulse oximetry (presence of amplitude of waveform possibly), and carotid blood flow (measured by Doppler) can be used to provide feedback on the effectiveness of the CPR delivered at a particular target depth. Based on the physiological information, the system can automatically determine a target CPR compression depth (e.g., calculate or look-up a new CPR compression target depth) and provide feedback to a rescuer to increase or decrease the depth of the CPR compressions. Thus, the system can provide both feedback related to how consistently a rescuer is administering CPR compressions at a target depth, and feedback related to whether the target depth should be adjusted based on measured physiological parameters. If the rescuers does not respond to such feedback and continues performed sub-optimal CPR, the system may then display an additional message to switch out the person performing CPR chest compressions.

In some examples, the system regularly monitors and adjusts the target CPR compression depth. In order to determine a desirable target depth, the system makes minor adjustments to the target CPR compression depth and observes how the change in compression depth affects the observed physiological parameters before determining whether to make further adjustments to the target compression depth. More particularly, the system can determine an adjustment in the target compression depth that is a fraction of an inch and prompt the rescuer to increase or decrease the compression depth by the determined amount. For example, the system can adjust the target compression depth by 0.1-0.25 inches (e.g., 0.1 inches to 0.15 inches, 0.15 to 0.25 inches, about 0.2 inches) and provide feedback to the rescuer about the observed compression depth based on the adjusted target compression depth. Then, over a set period of time, the system can observe the physiological parameters and, based on trends in the physiological parameters without making further adjustments to the target compression depth and at the end of the set time period, may determine whether to make further adjustments to the target compression depth.

And again, the actual performance of the rescuer against the revised target may be continually monitored to determine when the rescuer's performance has fallen below an acceptable level, so that the rescuer and perhaps others may be notified to change who is performing the chest compressions. Also, each of the relevant parameters of patient condition discussed above with respect to the various screenshots may be made one of multiple inputs to a process for determining when rescuers who are performing one component of a rescue technique should be switched out with another rescuer, such as for reasons of apparent fatigue on the part of the first rescuer.

The particular devices and displays shown in FIGS. 5A-8B may be implemented, as noted above, with a system that uses particular techniques to improve the accuracy of a prediction that an applied shock will be a success and that uses AMSA or other SPA values in making such a prediction. For instance, the feedback provided by the displays in the figures can be determined by selecting an appropriate ECG window size for calculating AMSA (e.g., one second or slightly longer, such as 1.5 seconds or 2 seconds), a window type (e.g., Tukey), and particular coefficients for the window. Such factors can also be changed over the time of a VF event, as discussed above, so as to maintain a most accurate predictor of defibrillation success.

While at least some of the embodiments described above describe techniques and displays used during manual human-delivered chest compressions, similar techniques and displays can be used with automated chest compression devices such as the AUTOPULSE device manufactured by ZOLL Medical Corporation of Chelmsford, Ma.

The particular techniques described here may be assisted by the use of a computer-implemented medical device, such as a defibrillator that includes computing capability. Such defibrillator or other device is shown in FIG. 9 , and may communicate with and/or incorporate a computer system 900 in performing the operations discussed above, including operations for computing the quality of one or more components of CPR provided to a victim and generating feedback to rescuers, including feedback to change rescuers who are performing certain components of the CPR. The system 900 may be implemented in various forms of digital computers, including computerized defibrillators laptops, personal digital assistants, tablets, and other appropriate computers. Additionally the system can include portable storage media, such as, Universal Serial Bus (USB) flash drives. For example, the USB flash drives may store operating systems and other applications. The USB flash drives can include input/output components, such as a wireless transmitter or USB connector that may be inserted into a USB port of another computing device.

The system 900 includes a processor 910, a memory 920, a storage device 930, and an input/output device 940. Each of the components 910, 920, 930, and 940 are interconnected using a system bus 950. The processor 910 is capable of processing instructions for execution within the system 900. The processor may be designed using any of a number of architectures. For example, the processor 910 may be a CISC (Complex Instruction Set Computers) processor, a RISC (Reduced Instruction Set Computer) processor, or a MISC (Minimal Instruction Set Computer) processor.

In one implementation, the processor 910 is a single-threaded processor. In another implementation, the processor 910 is a multi-threaded processor. The processor 910 is capable of processing instructions stored in the memory 920 or on the storage device 930 to display graphical information for a user interface on the input/output device 940.

The memory 920 stores information within the system 900. In one implementation, the memory 920 is a computer-readable medium. In one implementation, the memory 920 is a volatile memory unit. In another implementation, the memory 920 is a non-volatile memory unit.

The storage device 930 is capable of providing mass storage for the system 900. In one implementation, the storage device 930 is a computer-readable medium. In various different implementations, the storage device 930 may be a floppy disk device, a hard disk device, an optical disk device, or a tape device.

The input/output device 940 provides input/output operations for the system 900. In one implementation, the input/output device 940 includes a keyboard and/or pointing device. In another implementation, the input/output device 940 includes a display unit for displaying graphical user interfaces.

The features described can be implemented in digital electronic circuitry, or in computer hardware, firmware, software, or in combinations of them. The apparatus can be implemented in a computer program product tangibly embodied in an information carrier, e.g., in a machine-readable storage device for execution by a programmable processor; and method steps can be performed by a programmable processor executing a program of instructions to perform functions of the described implementations by operating on input data and generating output. The described features can be implemented advantageously in one or more computer programs that are executable on a programmable system including at least one programmable processor coupled to receive data and instructions from, and to transmit data and instructions to, a data storage system, at least one input device, and at least one output device. A computer program is a set of instructions that can be used, directly or indirectly, in a computer to perform a certain activity or bring about a certain result. A computer program can be written in any form of programming language, including compiled or interpreted languages, and it can be deployed in any form, including as a stand-alone program or as a module, component, subroutine, or other unit suitable for use in a computing environment.

Suitable processors for the execution of a program of instructions include, by way of example, both general and special purpose microprocessors, and the sole processor or one of multiple processors of any kind of computer. Generally, a processor will receive instructions and data from a read-only memory or a random access memory or both. The essential elements of a computer are a processor for executing instructions and one or more memories for storing instructions and data. Generally, a computer will also include, or be operatively coupled to communicate with, one or more mass storage devices for storing data files; such devices include magnetic disks, such as internal hard disks and removable disks; magneto-optical disks; and optical disks. Storage devices suitable for tangibly embodying computer program instructions and data include all forms of non-volatile memory, including by way of example semiconductor memory devices, such as EPROM, EEPROM, and flash memory devices; magnetic disks such as internal hard disks and removable disks; magneto-optical disks; and CD-ROM and DVD-ROM disks. The processor and the memory can be supplemented by, or incorporated in, ASICs (application-specific integrated circuits).

To provide for interaction with a user, the features can be implemented on a computer having an LCD (liquid crystal display) or LED display for displaying information to the user and a keyboard and a pointing device such as a mouse or a trackball by which the user can provide input to the computer.

The features can be implemented in a computer system that includes a back-end component, such as a data server, or that includes a middleware component, such as an application server or an Internet server, or that includes a front-end component, such as a client computer having a graphical user interface or an Internet browser, or any combination of them. The components of the system can be connected by any form or medium of digital data communication such as a communication network. Examples of communication networks include a local area network (“LAN”), a wide area network (“WAN”), peer-to-peer networks (having ad-hoc or static members), grid computing infrastructures, and the Internet.

The computer system can include clients and servers. A client and server are generally remote from each other and typically interact through a network, such as the described one. The relationship of client and server arises by virtue of computer programs running on the respective computers and having a client-server relationship to each other.

Many other implementations other than those described may be employed, and may be encompassed by the following claims. 

What is claimed is:
 1. A system for managing treatment for an emergency cardiac event, the system comprising: a memory; one or more electronic ports for receiving signals from sensors for obtaining an electrocardiogram (ECG) for a patient; a patient treatment module comprising computer readable instructions stored on a mass storage device and executable by one or more processing devices to: receive signals representing a time domain ECG of the patient from the one or more electronic ports, generate a first value indicating cardiac responsiveness to a therapeutic action calculated from a first set of frequency domain transform values corresponding to a first time segment of the time domain ECG, generate a second value indicating a current cardiac responsiveness to the therapeutic action calculated from a second set of frequency domain transform values corresponding to a second time segment of the time domain ECG, wherein the first time segment occurs prior to the second time segment, determine a difference between the second value indicating the current cardiac responsiveness to the therapeutic action and the first value indicating the cardiac responsiveness to the therapeutic action representing a change of the cardiac responsiveness to the therapeutic action from the first time segment to the second time segment, wherein the difference between the second value and the first value indicates an upward trend in the cardiac responsiveness to the therapeutic action when the difference is greater than a threshold increase, cause one or more output devices to display an indication of the second value indicating the current cardiac responsiveness to the therapeutic action, an indication of the upward trend in the cardiac responsiveness to the therapeutic action, and an indication of a magnitude of the difference between the second value and the first value representing the change of the cardiac responsiveness to the therapeutic action, the magnitude of the difference being greater than the threshold increase, the indication of the upward trend being different than another indication that is displayed when the difference between the second value and the first value indicates a decreasing or flat trend in the cardiac responsiveness to the therapeutic action, and receive a user input associated with the therapeutic action based on the indication of the second value indicating the current cardiac responsiveness to the therapeutic action, the indication of the upward trend in the cardiac responsiveness to the therapeutic action, and the magnitude of the difference between the second value and the first value representing the change of the cardiac responsiveness to the therapeutic action; and a patient treatment device comprising one or more defibrillating electrodes, the patient treatment device being coupled to the patient treatment module and being configured to selectively deliver a defibrillating shock to the patient based on the user input.
 2. The system of claim 1, wherein the first value indicating the cardiac responsiveness to the therapeutic action comprises an amplitude spectrum area (AMSA) value.
 3. The system of claim 1, wherein the first set of frequency domain transform values and the second set of frequency domain transform values are updated at a rate of 0.1-10 Hz.
 4. The system of claim 1, wherein the first and the second time segments are in a range between about 1 and 4 seconds.
 5. The system of claim 1, wherein the one or more processing devices generate the first set of frequency domain transform values and the second set of frequency domain transform values using a tapered window.
 6. The system of claim 5, wherein the tapered window is one of: a Tukey window, a Hann window, a Blackman-Harris window, or a Flat Top window.
 7. The system of claim 1, wherein the first set of frequency domain transform values and the second set of frequency domain transform values are generated using at least one of: Fourier, fast Fourier, discrete Fourier, Hilbert, discrete Hilbert, wavelet, and discrete wavelet methods.
 8. The system of claim 1, wherein the signals are received during a cardiac event.
 9. The system of claim 1, wherein the one or more output devices is configured to present an audible or visual feedback of the indication of the magnitude of the difference between the second value and the first value.
 10. The system of claim 9, wherein the audible or visual feedback comprises a message to prepare for shock administration.
 11. The system of claim 9, further comprising a CPR feedback module configured to control the one or more output devices to provide CPR feedback for a user.
 12. The system of claim 11, wherein the CPR feedback comprises instructions for the user to modify CPR administration.
 13. The system of claim 1, wherein the indication comprises one or more additional parameters.
 14. The system of claim 13, wherein the one or more additional parameters comprise: levels of prior successful defibrillations.
 15. The system of claim 1, wherein the indication of the magnitude of the difference between the second value and the first value comprises a likelihood of defibrillation shock success for the patient.
 16. The system of claim 1, wherein the patient treatment device is configured to initiate defibrillation treatment based at least in part on the change between the second set of frequency domain transform values and the first set of frequency domain transform values.
 17. The system of claim 1, wherein the first value indicating the cardiac responsiveness to the therapeutic action is calculated by averaging the first set of frequency domain transform values corresponding to the first time segment of the time domain ECG and the second value indicating the current cardiac responsiveness to the therapeutic action is calculated by averaging the second set of frequency domain transform values corresponding to the second time segment of the time domain ECG.
 18. The system of claim 1, wherein the difference between the second value and the first value comprises a positive value.
 19. The system of claim 1, further comprising: determine, based on the upward trend in the cardiac responsiveness, that the second value indicating the current cardiac responsiveness to the therapeutic action is within a threshold difference from a maximum expected value for cardiac responsiveness to the therapeutic action the maximum expected value representing a value from which an additional change of the cardiac responsiveness is expected to decrease; and cause the one or more output devices to display an indication that the second value indicating the current cardiac responsiveness to the therapeutic action is within the threshold difference from the maximum expected value for cardiac responsiveness to the therapeutic action.
 20. A method for managing treatment for an emergency cardiac event, the method comprising: receiving, by one or more processors, signals representing a time domain electrocardiogram (ECG) of a patient from one or more electronic ports; generating, by the one or more processors, a first value indicating cardiac responsiveness to a therapeutic action calculated from a first set of frequency domain transform values corresponding to a first time segment of the time domain ECG; generating, by the one or more processors, a second value indicating a current cardiac responsiveness to the therapeutic action calculated from a second set of frequency domain transform values corresponding to a second time segment of the time domain ECG, wherein the first time segment occurs prior to the second time segment; determining, by the one or more processors, a difference between the second value indicating the current cardiac responsiveness to the therapeutic action and the first value indicating the cardiac responsiveness to the therapeutic action representing a change of the cardiac responsiveness to the therapeutic action from the first time segment to the second time segment, wherein the difference between the second value and the first value indicates an upward trend in the cardiac responsiveness to the therapeutic action when the difference is greater than a threshold difference; causing, by the one or more processors, one or more output devices to display an indication of the second value indicating the current cardiac responsiveness to the therapeutic action, an indication of the upward trend in the cardiac responsiveness to the therapeutic action, and a magnitude of the difference between the second value and the first value representing the change of the cardiac responsiveness to the therapeutic action, the magnitude of the difference being greater than the threshold difference, the indication of the upward trend being different than another indication that is displayed when the difference between the second value and the first value indicates a decreasing or flat trend in the cardiac responsiveness to the therapeutic action; receiving, by the one or more processors, a user input associated with the therapeutic action based on the indication of the second value indicating the current cardiac responsiveness to the therapeutic action, the indication of the upward trend in the cardiac responsiveness to the therapeutic action, and the magnitude of the difference between the second value and the first value representing the change of the cardiac responsiveness to the therapeutic action; and in response to the user input, selectively generating, by the one or more processors, a signal for a defibrillating shock to be delivered to the patient.
 21. The method of claim 20, wherein the first value indicating the cardiac responsiveness to the therapeutic action comprises an amplitude spectrum area (AMSA) value.
 22. The method of claim 20, wherein the first set of frequency domain transform values and the second set of frequency domain transform values are updated at a rate of 0.1-10 Hz.
 23. The method of claim 20, wherein the first and the second time segments are in a range between about 1 and 4 seconds.
 24. The method of claim 20, wherein the first set of frequency domain transform values and the second set of frequency domain transform values are generated using a tapered window.
 25. The method of claim 24, wherein the tapered window is one of: a Tukey window, a Hann window, a Blackman-Harris window, or a Flat Top window.
 26. The method of claim 20, wherein generating the first set of frequency domain transform values and the second set of frequency domain transform values comprises at least one of: Fourier, fast Fourier, discrete Fourier, Hilbert, discrete Hilbert, wavelet, and discrete wavelet methods.
 27. The method of claim 20, wherein the second set of frequency domain transform values are generated via processing of multiple earlier time segments from the second time segment of the ECG.
 28. The method of claim 20, wherein the signals are received during a cardiac event.
 29. The method of claim 20, wherein the indication of the magnitude of the difference between the second value and the first value comprises a likelihood of defibrillation shock success for the patient.
 30. The method of claim 20, wherein selectively generating the signal for the defibrillating shock to be delivered to the patient is based at least in part on the change between the second set of frequency domain transform values and first set of frequency domain transform values.
 31. The method of claim 20, further comprising generating an audible or a visual feedback comprising a message to prepare for the defibrillating shock. 